Systems and Methods to Display Cardiac Signals Based on a Signal Pattern

ABSTRACT

Systems, methods, and computer program product embodiments are disclosed for displaying cardiac signals based on a signal pattern. An embodiment operates by accessing an input cardiac signal. The embodiment matches a portion of the input cardiac signal to a known signal pattern. The embodiment then displays an indication of a degree of the match.

CROSS-REFERENCES TO RELATED APPLICATIONS

The present application claims the benefit and priority to PCT Application No. PCT/US2019/031434, filed May 9, 2019, entitled “Systems And Methods To Display Signals Based On A Signal Characteristic,” which claims the benefit and priority to U.S. Provisional Patent Application No. 62/669,345, filed May 9, 2018, entitled “Acquisition and Preservation of Electrical Signal Information in a Multi-Signal-Source Environment,” both of which are incorporated herein by reference in their entireties.

TECHNICAL FIELD

Embodiments included herein generally relate to cardiac electrophysiology (EP) signal acquisition and recording systems. More particularly, system, apparatus, and method embodiments are disclosed for conveying biomedical signals between a patient and monitoring and treatment devices.

BACKGROUND

Catheter ablation is a procedure to treat arrhythmias such as atrial fibrillation, a disease of the heart muscle characterized by abnormal conduction. Depending on the severity of the problem, multiple ablation procedures may be necessary to achieve effective results. This is because current electrophysiology (EP) technology has limitations in precisely locating the tissue to ablate that is the source of the abnormality.

The conventional diagnostic process starts with an electrocardiogram (ECG) taken from electrodes attached to the surface of the skin of a subject (e.g., a patient). A medical team evaluates the ECG signal and determines whether medication and/or ablation are/is indicated. If ablation is indicated, an EP study is performed. A catheter is inserted into the heart via the patient's neck or groin and the electrical activity of the heart is recorded. Based on this EP study, ablation is performed on the area(s) of the heart that the medical team suspects is causing the abnormal heart rhythm(s).

An ablation catheter is inserted into the patient's blood vessel and guided to the site of the tissue that is causing the abnormal electrical propagation in the heart. The catheter may use different energy sources (the most common being heat or cold) to scar the tissue, reducing its ability to initiate and/or transmit abnormal electrical impulses, which eliminates the abnormal heart rhythm. ECG signals are recorded from a surface electrode on a patient's skin, and intracardiac (IC) signals may be obtained from catheters inside the patient's heart and recorded as an electrogram (EGM). Both ECG and IC (EGM) signals are small signals that require conditioning and amplification to be accurately evaluated.

In conventional EP systems, to confirm whether the ablation treatment of a certain tissue site is successful, the medical team must often stop the ablation process and collect physiologic signals (e.g., cardiac) from a monitoring device (e.g., ECG monitor). This is because current systems do not allow accurate simultaneous detection, acquisition, and isolation of small cardiac signals (amplitude in the range of 0.1-5 mV and frequency in the range of DC to 1 KHz) in near real-time during the application of large ablation signals (on the order of a few hundred volts at frequencies around 450 kHz).

Specifically, U.S. Patent Application Publication No. US 2006/0142753A1 to Francischelli, et al. propose a system and method for ablation and assessing their completeness or transmurality by monitoring the depolarization ECG signals from electrodes adjacent to the tissue to be ablated. Francischelli, et al. point out that, to minimize noise-sensing problems during measurements of the ECG signals from the electrodes on the ablation device, the measurements are preferably made during interruptions in the delivery of ablation energy to the ablation electrodes.

Generally, some current EP recording systems can effectively support treatment of arrhythmias such as atrial flutter and supra ventricular tachycardia, which show up as large-amplitude, low-frequency signals. However, more complex and prevalent arrhythmias, such as atrial fibrillation and ventricular tachycardia, which are characterized by low-amplitude, high-frequency signals, have not found effective evaluation of all relevant signals.

This signal detection, acquisition, and feature extraction can be further complicated by equipment line noise and pacing signals. To reduce noise and artifacts from the various electrical signal information, current EP recorders use low-pass, high-pass, and notch filters. Unfortunately, conventional filtering techniques can alter signals and make it difficult or impossible to see low-amplitude, high-frequency signals that can be inherent in cardiac monitoring, the visualization of which signals could help treat atrial fibrillation and ventricular tachycardia. It has been recently recognized that the assurance of waveform integrity, such as for low noise acquisition of IC and ECG signals in an EP environment, had not been previously accomplished due to contamination by artifacts and noise.

Specifically, in an article titled Waveform Integrity in Atrial Fibrillation: The Forgotten Issue of Cardiac Electrophysiology (Annals of Biomedical Engineering, Apr. 18, 2017). Martinez-Iniesta, et al point out that high-frequency and broadband equipment noise is “unavoidably recorded” during signal acquisition, and that further complications of acquisition result from a variety of other signals, including 50 or 60 Hz electrical mains, high-frequency patient muscle activity, and low-frequency baseline wander from respiratory or catheter movements or unstable catheter contact. Martinez-Iniesta, et al. further point out that regular filtering causes significant alteration of waveforms and spectral properties, as well as poor noise reduction. Yet aggressive filtering between 30 and 300 Hz is still a routine EP practice.

Conventional practices distort morphological features in resulting signals, causing loss of relevant (of interest) signal information and affecting signal validity. Martinez-Iniesta, et al propose a partial software solution for only mid- and high-frequency noise reduction using preprocessing and de-noising methods, yet no solution exists combining low-frequency noise-reduction components in software with noise-reduction components in hardware. A desired feature of EP systems is the ability to preserve the integrity of original signal information using a combination of hardware and software that can reduce noise from signals (or promote a high signal-to-noise ratio) while minimizing hardware filtering that would otherwise remove signal content of interest.

Currently, the predominant approach for ablation treatment of paroxysmal and persistent atrial fibrillation is pulmonary vein isolation (PVI), wherein a medical team, using a cardiac mapping system, recreates the heart geometry in 3D and performs ablation on anatomical locations such as the pulmonary vein from which the atrial fibrillation emanates. The procedure is a long 2-8 hours, and a physician may not achieve a durable lesion/scar to isolate the tissue causing the problem from the left atrium. Thus, patients are often required to return for additional ablation procedures to complete the treatment. However, additional ablation procedures, and possible complications, can be minimized by being able to clearly visualize the cardiac signals during ablation and determine whether an ablation lesion is transmural.

Conventional EP systems may suffer from several other limitations. First, a user often wants to process and display multiple features of signals in near real-time. For example, a medical team may want to simultaneously display various and multiple versions of ECG, IC, and other physiologic signals in near real-time to evaluate different signal attributes. But conventional EP systems are often unable to simultaneously process and display multiple versions of signals in near real-time.

Second, a user often wants to dynamically apply a new digital signal processing function to a signal without interfering with other digital signal processing functions already being applied to the signal. But conventional solutions do not enable a user to dynamically apply a new digital signal processing function to a signal without stopping the capture of the signal, or interfering with other digital signal processing functions already being applied to the signal.

Finally, a user often wants to synchronize the processing and display of multiple signals in near real-time. For example, a user may want to synchronize the display of multiple processed versions of the same signal. Further, a medical team may want to synchronize the display of multiple processed versions of ECG, IC, and other physiologic signals. This is because the ability of the medical team to make an effective clinical diagnosis may depend on comparing multiple signals at the same point in time. But conventional solutions may not be able to process and synchronize the display of multiple processed signals in near real-time.

SUMMARY OF THE EMBODIMENTS

Apparatus, systems, and methods are disclosed for EP signal acquisition and recording with multiple improvements in noise and artifact reductions in various biomedical applications.

The embodiments of the disclosed EP system can record raw (unaltered) cardiac and other physiologic signals with multiple display options and with low noise and large input signal dynamic range. Raw signals acquired by an acquisition module are filtered and processed in accompanying software using a digital processing module, with minimal use of filters in the hardware (e.g., hardware filters are only used for AC coupling, anti-aliasing, and RF suppression). The use of software-based digital signal processing algorithms allows the display of signals in real-time as a raw signal, or as a combination of raw and processed signals simultaneously in real-time in a single window or in multiple windows. Furthermore, the visualization and review capabilities of the disclosed EP system allow a user to mark features specified in algorithms on real-time tracings.

The disclosed EP system allows for the display of signals with more than one signal processing algorithm applied at the same time, a feature not found in conventional systems. This allows a user to look at signals filtered in multiple ways for specific reasons. In the real-time window, waveforms of interest can be displayed as raw signals or as any combination of raw and filtered signals to enable better visualization of signals in the presence of noise and artifacts.

All displayed signals are time synchronized. The user has the option of opening multiple review windows, with the ability to display the results of various signal-processing algorithms, independent of the real-time tracings.

From a clinical perspective, the disclosed EP system can significantly assist in a medical team's decision making for patients undergoing various medical therapies (such as ablation), with benefits including, but not limited to: suppression of RF energy for cleaner, more reliable recordings of intracardiac signals, less baseline wander, and noise reduction; improved dynamic range for better visualization, especially of very low amplitude signals temporally situated within large-amplitude signals; real-time digital processing and recording of raw signals to facilitate signal filtering without affecting original information and to reduce artifacts and noise; high-quality unipolar signals to assist in the determination of tissue type and catheter location; improved waveform integrity and reduced artifacts that are byproducts of signal processing, allowing a medical team to enhance procedure outcomes; and improved signal information, allowing a medical team to provide more accurate catheter tip position for ablation and other therapeutic levels and durations for therapy effectiveness.

In some embodiments of a system for visualization of signals using a late potential, a memory comprises a first signal module comprising a first digital signal processor (DSP) configured to match a beat in a first packet associated with a first cardiac signal to a known signal characteristic, and a second signal module comprising a second DSP configured to search for the late potential in a second packet associated with a second cardiac signal in response to the matching. The memory also comprises a display module coupled to the first signal module and the second signal module, the display module configured to display a portion of the first cardiac signal and display a portion of the second cardiac signal comprising the late potential time-synchronized to the displayed portion of the first cardiac signal based on the searching. The system also comprises at least one processor coupled to the memory and configured to execute the first signal module, the second signal module, and the display module. The execution of the system components by a computer system implement various method embodiments for visualizing signals using a late potential. The computer system comprises a non-transitory computer-readable device having instructions stored thereon that, when executed by at least one computing device, cause the at least one computing device to perform operations implementing the method steps.

In some embodiments of a system for visualization of signals using an early activation, a memory comprises a first signal module comprising a first DSP configured to match a beat in a first packet associated with a first cardiac signal to a known signal characteristic, and a second signal module comprising a second DSP configured to search for the early activation in a period of time before the matched beat in a second cardiac signal. The memory also comprises a display module coupled to the first signal module and the second signal module, the display module configured to display a portion of the first cardiac signal and display a portion of the second cardiac signal comprising the early activation time-synchronized to the displayed portion of the first cardiac signal based on the searching. The system also comprises at least one processor coupled to the memory and configured to execute the first signal module, the second signal module, and the display module. Some method embodiments and non-transitory computer-readable device embodiments are also disclosed for visualization of signals using an early activation.

Some method and non-transitory computer-readable device embodiments implement steps comprising accessing a first cardiac signal associated with a surface lead, matching a beat of the first cardiac signal to a known signal pattern, and searching for a period of time before and after the matched beat for an early activation or a late potential in a second cardiac signal.

Other method and non-transitory computer-readable device embodiments, for filtering noise from an input signal using notch filtering, implement the steps of: accessing an input signal having a first harmonic frequency and having noise; determining a quiet period in the input signal; during the quiet period, storing samples of the noise of the input signal in a buffer; subtracting the samples from a single cycle of the noise in the buffer from the input signal to create a filtered signal, wherein the subtracting removes the first harmonic frequency and a second harmonic frequency from the input signal and avoids introducing transient responses in the filtered signal; and repeating the determining, storing, and subtracting to refine the filtered signal.

Some method and non-transitory computer-readable device embodiments, for filtering noise from an input signal using high frequency filtering, implement the steps of accessing an input signal comprising noise and a high frequency signal of interest; high pass filtering the input signal to create a filtered signal; isolating an artifact associated with the noise in the filtered signal from the high frequency signal of interest; optionally selecting a filter based on the isolated artifact, and blanking the filtered signal for a fixed period of time before and after the isolated artifact, wherein the blanking removes the isolated artifact, optionally using the selected filter, and allows passage of the high frequency signal of interest.

Some method and non-transitory computer-readable device embodiments for pattern matching implement the steps of: accessing an input cardiac signal; matching a portion of the input cardiac signal to a known signal pattern; and displaying an indication of the degree of the match. Other embodiments for pattern matching match a portion of the input cardiac signal to a known signal pattern based on a detection threshold and display a highlighted portion of the input cardiac signal based on the matching.

System embodiments are also disclosed for producing a clean unipolar signal, comprising an electrocardiogram (ECG) circuit board configured to process an ECG signal and a plurality of intracardiac (IC) circuit boards, each configured to process a corresponding IC signal, wherein the ECG circuit board and the plurality of IC circuit boards share substantially the same circuit configuration and components, and the ECG circuit board processes the ECG signal using substantially the same path as each IC circuit board uses to process its corresponding IC signal.

Other system embodiments are disclosed for performing electrophysiology (EP) processing, comprising an ECG circuit board configured to receive an ECG signal, a plurality of IC circuit boards, each configured to receive an IC signal, a communications interface communicatively coupled to a remote device, and a processor, coupled to the ECG board, the plurality of IC circuit boards, and the communications interface. Such system embodiments may he configured to receive, via the communications interface, feedback from the remote device, and control, via the communication interface, the remote device based on the ECG signal, the IC signals, and the feedback from the remote device.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated herein and form part of the specification, illustrate the present embodiments and, together with the description, further serve to explain the principles of the present embodiments and to enable a person skilled in the relevant art(s) to make and use the present embodiments.

FIG. 1 illustrates a block diagram of a conventional electrophysiology (EP) environment with patient connections and sources of interference.

FIG. 2 illustrates a hardware system block diagram of the disclosed EP hardware system, according to some embodiments.

FIG. 3 illustrates a block diagram of a multi-channel analog-to-digital input/output of the EP hardware system input stage, according to some embodiments.

FIG. 4 illustrates a block diagram of a single channel of the EP hardware system input stage, according to some embodiments.

FIG. 5A illustrates a block diagram of the overall EP system, according to some embodiments.

FIG. 5B illustrates a high-level abstraction of the overall EP system hardware and software, according to some embodiments.

FIG. 6A illustrates a schematic diagram of the large-signal input protection portion of the input protection circuit of the EP hardware system, according to some embodiments.

FIG. 6B illustrates a schematic diagram of the electrostatic discharge (ESD) protection portion of the input protection circuit of the EP hardware system, according to some embodiments.

FIG. 7 illustrates a schematic diagram of the radio frequency (RF) filtering portion of the input protection circuit of the EP hardware system, according to some embodiments.

FIGS. 8A-8E illustrate voltage signal plots of a typical defibrillation signal at the input to the input protection circuit, according to an exemplary embodiment.

FIGS. 9A-9E illustrate voltage signal plots of a typical ablation signal at the input to the input protection circuit, according to an exemplary embodiment.

FIG. 10 illustrates a schematic diagram of the instrumentation and gain stages of the EP hardware system, according to some embodiments.

FIG. 11 illustrates a schematic diagram of a large-signal detection/fast recovery circuit of the EP hardware system, according to some embodiments.

FIG. 12 illustrates a voltage signal plot showing the slow recovery that occurs after a large unwanted signal survives the input protection, instrumentation, and gain stages of the EP hardware system circuitry when the large-signal detection/fast recovery circuit is disconnected, according to an exemplary embodiment.

FIGS. 13A-13C illustrate voltage signal plots showing the fast recovery that occurs after a large unwanted signal is presented to the input protection, instrumentation, and gain stages of the EP hardware system circuitry when the large-signal detection/fast recovery circuit is connected, according to an exemplary embodiment.

FIGS. 14A-14D illustrate signal plots for voltage signals at various internal nodes through the large-signal detection/fast recovery circuit when it is connected, according to an exemplary embodiment.

FIGS. 15A-15B illustrate signal plots for current signals over the resistors at the output of the connected large-signal detection/fast recovery circuit, according to an exemplary embodiment.

FIG. 16 illustrates a schematic diagram of a low-frequency feedback circuit that serves as a dynamic current source for the EP hardware system, according to some embodiments.

FIGS. 17A-17D illustrate signal plots for typical in-band voltage differential input signals that are affected by 60 Hz common-mode noise into the EP hardware system, according to an exemplary embodiment.

FIGS. 18A-D illustrate signal plots of a typical differential voltage signal affected by 601 z common-mode noise as it travels through the EP hardware system, according to an exemplary embodiment.

FIGS. 19A-D illustrate signal plots of a typical 500 kHz ablation input signal that is in a frequency range to be attenuated by the RF filter of the EP hardware system, according to an exemplary embodiment.

FIGS. 20A-20B illustrate signal plots of a typical 500 kHz ablation input signal at the shield inputs that enable the RF filter to attenuate the input signal to the EP hardware system, according to an exemplary embodiment.

FIGS. 21A-21D illustrate signal plots of a typical 500 kHz ablation input signal that has been attenuated after it has traveled through the instrumentation amplifier and after it has traveled through the fully differential op amps of the EP hardware system, according to an exemplary embodiment.

FIG. 22A illustrates the improvement in the visualization of an ECG or IC signal, according to an exemplary embodiment.

FIG. 22B illustrates the EP system's ability to reveal low-amplitude cardiac signals and micro-components of artifacts of an EP signal in the presence of noise and large-signal procedures, according to an exemplary embodiment.

FIG. 22C illustrates the EP system's ability to remove 60 Hz noise, without saturation or delayed recovery, while preserving the component of the 60 Hz signal that belongs to the original waveform, according to an exemplary embodiment.

FIG. 23 illustrates a schematic diagram of an improved Wilson Central Terminal-Right Leg Drive (WCT-RLD) circuit, according to some embodiments.

FIG. 24 illustrates a schematic diagram of a Twin-T feedback network interfaced with an RLD circuit of a WCT-RLD circuit, according to some embodiments.

FIG. 25 illustrates a signal plot of the output of a Twin-T feedback network of a WCT-RLD circuit, according to an exemplary embodiment.

FIG. 26 is a block diagram of a system for processing and displaying multiple signals in near real-time, according to some embodiments.

FIG. 27 is a block diagram of a queuing module for the storage of generated packets associated with different base signals, according to some embodiments.

FIG. 28 is a block diagram of a configuration path module for generating at runtime time-aligned signals that are processed from a set of base signals, according to some embodiments.

FIG. 29 is a block diagram of a signal module generated by a signal factory module, according to some embodiments.

FIG. 30 is a block diagram of a display module for displaying one or more signals, according to some embodiments.

FIG. 31 is a block diagram of a monitoring module for performing error checking, according to some embodiments.

FIG. 32 illustrates an example adjustment of a sweep speed for a display module, according to some embodiments.

FIG. 33 illustrates signal management for a display module, according to some embodiments.

FIG. 34 illustrates an example adjustment of zoom and clip factors for a display module, according to some embodiments.

FIG. 35 illustrates pattern search management for a display module, according to some embodiments.

FIG. 36 illustrates a late potential search result highlighted in a display of a display module, according to some embodiments.

FIG. 37A illustrates using a display module configured as waterfall view, according to some embodiments.

FIG. 37B illustrates the correspondence between signals in a regular display module and a display module configured as waterfall view, according to some embodiments.

FIG. 37C illustrates using a display module configured as dynamic view, according to some embodiments.

FIG. 37D illustrates using display module configured as trigger view, according to some embodiments.

FIG. 38 illustrates the capture of signals in a display of a display module configured as a review window, according to some embodiments.

FIG. 39 illustrates amplitude measurement performed in a display of a display module configured as a review window, according to some embodiments.

FIG. 40 is a flowchart for a method for processing and displaying multiple signals in near real-time, according to an embodiment.

FIG. 41 is a flowchart for a method for configuring one or more signal modules, according to some embodiments.

FIG. 42 is a flowchart for a method for generating a signal module from a signal processing specification, according to some embodiments.

FIG. 43 is a flowchart for a method for equalizing the processing delay associated with each DSP of the one or more signal modules, according to some embodiments.

FIG. 44 is a flowchart for a method for receiving one or more signal samples for one or more signals using an input module, according to some embodiments.

FIG. 45 is a flowchart for a method for converting one or more signal samples to one or more packets using a packetizer, according to some embodiments.

FIG. 46 is a flowchart for a method for dispatching a packet containing one or more signal samples to a queueing module, according to some embodiments.

FIG. 47 is a flowchart for a method for dispatching a packet from a queuing module to a signal module associated with the packet, according to some embodiments.

FIG. 48 is a flowchart for a method for processing a packet using a signal module associated with the packet, according to some embodiments.

FIG. 49 is a flowchart for a method for displaying a processed packet to a display screen using a display module, according to some embodiments.

FIG. 50 illustrates an example of a signal with superimposed noise, according to some embodiments.

FIG. 51 illustrates an example of a conventional approach to removing noise using a notch filter, according to some embodiments.

FIG. 52 illustrates an example of the result of applying the conventional filter of FIG. 51, according to some embodiments.

FIG. 53 illustrates an example of a 180 Hz harmonic still present at the output of the conventional filter of FIG. 51, according to some embodiments.

FIG. 54 illustrates an example of notch filtering for a signal with 60 Hz and 180 Hz noise, according to some embodiments.

FIG. 55 illustrates an example of a notch filter that uses 100 samples and stores exactly 3 cycles of 60 Hz, according to some embodiments.

FIG. 56 illustrates an example of the notch filter that calculates quiet times, according to some embodiments.

FIG. 57 illustrates an example of a notch filter that accumulates a replica of noise and subtracts it from a noisy signal, according to some embodiments.

FIG. 58 illustrates an example of the result of a notch filter, according to some embodiments.

FIG. 59 is a flowchart for a process for notch filtering noise from an input signal, according to some embodiments.

FIG. 60 illustrates an example of a conventional high-pass filter, according to some embodiments.

FIG. 61 illustrates an example of a signal containing both high frequency signals from the conduction areas of the heart as well as sharp local spikes from various sources, according to some embodiments.

FIG. 62 illustrates an example of the resulting output of filtering the signal of FIG. 61 using the high-pass filter of FIG. 60, according to some embodiments.

FIG. 63 illustrates an example of the resulting output of filtering the signal of FIG. 61 using a high-pass filter that removes an impulse while allowing passage of a high frequency signal of interest, according to some embodiments.

FIG. 64 is a flowchart for a process for high-pass filtering noise from an input signal, according to some embodiments.

FIG. 65 illustrates an example of a review window for selecting a range of data using vertical calipers, according to some embodiments.

FIG. 66 illustrates an example of saving a selected pattern as a reference beat, according to some embodiments.

FIG. 67 illustrates an example of a window of selectable patterns to search, according to some embodiments.

FIG. 68 illustrates an example of a pattern search summary view in the review window of FIG. 65 where multiple matching patterns are displayed, according to some embodiments.

FIG. 69 illustrates an example of a pattern search summary view in the review window of FIG. 68 where a single matching pattern is displayed while other patterns are hidden, according to some embodiments.

FIG. 70 illustrates an example of a detail view for the review window of FIG. 65, according to some embodiments.

FIG. 71 illustrates an example of pattern match confidence values provided by lead, according to some embodiments.

FIG. 72 is a flowchart for a process for pattern matching, according to some embodiments.

FIG. 73 is a flowchart for a process for pattern matching, according to some embodiments.

FIG. 74 illustrates an example of a search definitions window for creating and managing searches for late potentials and early activations, according to some embodiments.

FIG. 75 illustrates an example of a late potential detection configuration window for defining various search parameters for late potentials, according to some embodiments.

FIG. 76 illustrates an example of showing the positions of late potentials along with their detection confidences, according to some embodiments.

FIG. 77 illustrates an example of an early activation detection configuration window for defining various search parameters for early activations, according to some embodiments.

FIG. 78 illustrates an example of showing the positions of early activations along with their detection confidences, according to some embodiments.

FIG. 79 illustrates an example of a search definitions window for managing already defined late potential and early activation searches, according to some embodiments.

FIG. 80 is a flowchart for a process for detecting early activations or late potentials, according to some embodiments.

FIG. 81 illustrates an example of a waterfall display configuration window, according to some embodiments.

FIG. 82 illustrates an example of a waterfall view using time mode, according to some embodiments.

FIG. 83 illustrates an example of a waterfall view using beat mode, according to some embodiments.

FIG. 84 illustrates an example of a display parameters window, according to some embodiments.

FIG. 85 illustrates an example computer system, according to some embodiments.

The features and advantages of the present embodiments will become more apparent from the detailed description set forth below when taken in conjunction with the drawings, in which like reference characters identify corresponding elements throughout. In the drawings, like reference numbers generally indicate identical, functionally similar, and/or structurally similar elements. The drawing in which an element first appears is indicated by the leftmost digit(s) in the corresponding reference number.

DETAILED DESCRIPTION OF THE INVENTION

Apparatus, systems, and methods related to a unique amplifier topology are disclosed for conditioning cardiac (e.g., ECG and IC) and other physiologic signals, specifically to clearly define and record low-amplitude, low-frequency information, which may be acquired during ablation and other similar large-signal perturbations, such as pacing and stimulation. During procedures, the tip of a catheter (or other electrodes) can be connected to pacing, ablation, and stimulator systems to allow visualization, pacing, ablation, and stimulation without mode switching. For example, the disclosed apparatus, systems, and methods can effectively separate ablation signals from cardiac signals during ablation while simultaneously providing input protection against high voltage, such as from defibrillation signals. Similarly, the disclosed apparatus, systems, and methods can effectively separate stimulation signals from physiologic signals during stimulation.

As different system recording requirements cannot be satisfied simultaneously for each signal type, each block, or module, of the system can be performance optimized to achieve multiple signal conditioning requirements desired by clinicians. The various embodiments can enable the system to handle cardiac, pacing, ablation, defibrillation, stimulator, and other physiologic signal types simultaneously by detecting, conditioning, and displaying the signal of interest, to monitor, for example, the effect of an ongoing procedure on a cardiac signal.

Additionally, the various embodiments can ensure the acquisition of multiple low-amplitude cardiac signals in the presence of numerous sources of electrical noise and environmental interference aside from the large signals injected during ablation and stimulation procedures, pacing, or defibrillation. The cardiac signals of interest can also be displayed in an uncomplicated and clinically-relevant way, processing the signals in real-time, or near-real-time, to display a comprehensive cause-and-effect relationship between physician-initiated procedures and resulting cardiac signals, while contemporaneously identifying signal artifacts and removing unwanted noise. This disclosure identifies both hardware and software embodiments to achieve these objectives.

This disclosure refers to both “unipolar” and “bipolar signals,” which are both widely used in EP recordings, but for complementary purposes. Both unipolar and bipolar signals are taken from the potential difference recorded at two (or more) different, separated electrodes on a patient's body, specifically the limbs and chest of the patient, for example, to measure ECG signals, or at two (or more) different, separated catheters placed directly on cardiac tissue, for another example, to measure IC signals.

It is conventional to use a 12-lead ECG system consisting of a connection to each of the limbs: right arm (RA), left arm (LA), right leg (RL), and left leg (LL), and six precordial connections V1 through V6 from six separate electrodes placed at various locations on the patient's chest. The individual ECG electrode wires are connected to a terminal block at the end of a patient table, routing from there to a data acquisition system. All leads are conventionally connected to protection circuitry to prevent damage to the instrumentation caused by defibrillation potentials or static electricity from the environment.

Bipolar signals are standard for certain ECG measurements (lead I, II, III), but they may also be obtained directly from the heart surface to collect IC signals. Bipolar signals may be obtained by attaching two (or more) electrodes in close proximity in a specific area of the heart or cardiac tissue and measuring the potential difference between the electrodes, providing information about local electrical activity, such as late potentials caused by damaged heart muscle. Bipolar IC signals do not, however, provide information about electrical impulse propagation direction. For instance, one of the difficulties with bipolar mapping presently is failure to know whether a signal of interest is arising from the distal or proximal electrode. This is important because pacing and energy delivery are provided through the distal electrode.

Unipolar signals arise from a point source, such as may be obtained from an IC potential, by placing one IC electrode on the surface of the patient's heart and the other electrode at a distance from the first to serve as a reference signal. Unipolar leads from IC electrodes are connected in such a way that one lead serves as the active lead while the other lead(s) is/are at an inactive location or the result of a calculated inactive location (WCT, discussed below). In this way, the current flowing towards the active electrode produces a positive deflection, while current flowing away from the active electrode produces a negative deflection. This provides information about cardiac signal propagation direction. Unipolar recordings are especially useful when directionality information is desired, such as in the determination of depolarization and repolarization pathways in the endocardium and epicardium. Disclosed herein is a method using first order derivatives of both unipolar signals.

Leads may also be connected to the limbs to create an imaginary triangle called “Einthoven's triangle.” In this way, true bipolar leads can be obtained by referencing each connection to one of the other two (e.g., LA referenced to RA is Lead I; LL to RA is Lead II, and finally, LA to LL is Lead III). Then, an average of the three limb wires RA, LA, and LL can approximate a zero potential point to provide a reference electrode (WCT, discussed below). Here, the vector sum of Lead I and Lead III is Lead II.

Using the concept of Einthoven's triangle, the Wilson Central Terminal (WCT) is an electrical circuit concept used in the art (and discussed further in this disclosure) that can be used as an indifferent electrode that acts as an electrical center of the heart as a reference. The WCT can be used when IC signals are desired to be displayed in unipolar fashion. When using the WCT as a reference for unipolar signals, the unipolar signals can approximate widely-spaced bipolar signals for consistent unipolar recording. The WCT can prevent an additional catheter from having to be used as a reference for unipolar recordings of IC signals.

In this disclosure, “near real-time” refers to the acquisition and visualization of signals through the EP system from the time they occur at the input of the hardware circuitry of the EP system to the time they are first displayed on the EP system display monitor(s), either in raw (unprocessed) form or after being processed by the EP system Main Processing Unit (MPU) and one or more digital signal processing (DSP) module(s). “Near real-time” for a raw signal can be less than approximately five (5) milliseconds, and for a processed signal can be less than approximately fifty (50) milliseconds.

FIG. 1 is a block diagram representing a conventional EP environment 100 with patient connections and sources of interference. As understood by a person of ordinary skill in the art, the patient 118 may be connected to diagnostic equipment such as a pulse oximeter 104, one or more ECG units 106, an infusion pump 108, an electroanatomic mapping system 110, a data acquisition system 112, such as the EP system disclosed herein, an ablation generator 114, a nerve stimulator 128, and other diagnostic equipment, such as an external defibrillator, and several IC catheters. Such diagnostic equipment can be connected to and can be powered by 120-240V, 50/60 Hz AC power mains 102. The laboratory diagnostic equipment can be connected to earth ground 120, through its power source connection.

As the number of connections to the patient 118 increases, the leakage current 122 from all patient connections through the patient 118 to earth ground 120 increases, increasing the likelihood of interference and adverse effects. Total leakage current 122 when such equipment is connected and operating at the same time may safely and allowably be up to several tens of microamperes at a fundamental mains frequency of 50 or 60 Hz, with harmonics extending to several thousand Hertz. This leakage current 122 can interfere substantially with the processing of ECG and IC signals. Furthermore, the patient 118 can be both capacitively coupled 124 and inductively coupled 126 to the 120/240 AC power mains 102. The patient 118 may additionally pick up RF interference 116 from equipment in proximity to the EP environment, such as wireless headsets, mobile phones, and wireless monitors.

For reference, TABLE 1 outlines signals that may be found in a conventional medical instrumentation/EP environment, both wanted and unwanted, and their signal characteristics.

TABLE 1 Signal characteristics in a conventional EP environment Signal Amplitude/ Signal Type Output Frequency Nature/Use of Signal ECG (cardiac skin 0.5 to 4 mV 0.01 to 250 Hz Conventionally required electrodes) for cardiac monitoring IC (intracardiac leads) 20 μV to 10 mV 0.05 to 500 Hz Conventionally required for cardiac monitoring EGG 10 μV to 1000 μV DC to 1 Hz Smallest biomedical signal (electrogastrography) of interest (non-EEG) RF Ablation System RF output: 100 W, 300-600 kHz, Conventional equipment 100 s of V 460-500 kHz used during EP study typical Defibrillation 4500 to 5000 V 10 s of ms Possible equipment used in duration EP environment Pacing Cardiac 0.1 to 25 mA, 27 Vmax 0.5 to 10 ms Conventional equipment Stimulator duration; up to used during EP study 1000 μs pulse width; up to 1200 Hz Equipment power-line 2 Vpp typical 60 Hz, 180 Hz Conventional lab noise harmonic environment power

As a result of equipment noise and other EP environment interference, measured voltages on a patient's body can be upwards of 1-3 V RMS (root mean squared) over a frequency spectrum ranging from 50 Hz to several tens of megahertz. Yet, the amplitude of cardiac signals can measure in the range of 25 microvolts to 5 mV. To display these signals amongst the noisy environment, the cardiac signals are conventionally amplified and displayed with no loss of detail (so as not to miss relevant information, for example) and minimal added noise (so as not to cover up signal details, for example), while delivering RF ablation energy at about 70 V RMS at 500 kHz, or cardiac stimulation up to 25 mA, for example.

To properly acquire and identify cardiac signals of interest in such an environment, a very high signal-to-noise (SNR) ratio (on the order of 30 dB) is desirable but not achievable without an approach to minimize or eliminate sources of electrical interference before having to process them electrically through software methods. Conventional hardware approaches used to condition the signals in such a noisy environment include shielding of cables, grounding of equipment, balancing inputs and outputs, differential amplification, filtering, lowering circuit impedances, electric isolation, or signal enhancement techniques. These conventional methods have had limited success in achieving sufficient SNR.

The disclosed hardware embodiments can decrease interference while applying novel electrical circuit topology to minimize noise, isolate the IC and ECG signals of interest, condition those signals, and remove unwanted artifacts. This can be done before the signals are passed to processing software that provides an electrophysiologist the power of near real-time visualization and comprehensive signal review. Embodiments of the EP system described herein can achieve considerable SNR improvement.

FIG. 2 is a hardware system block diagram representing the disclosed EP hardware system 200, including, for example, an EP workstation 201 and an EP console 214, according to some embodiments. The system can include an EP console 214 with an optical interface 216 of the EP measurement hardware from a user input, visualization, and review workstation (herein, “EP workstation” 201). The EP workstation 201 can include, for example, a conventional laboratory PC 208 with a keyboard/mouse 210 and a monitor splitter 206 facilitating multiple monitors 202, 204 to provide multiple-signal, multiple-context display capability for EP signal visualization and review software. The EP workstation 201 can also include an additional optical interface 212 for electrically isolated data transmission from the EP console 214 over USB 2.0, for example.

The EP console 214 can include one or more ECG amplifiers 218, one or more unipolar amplifiers 220 to process unipolar signals, and one or more bipolar amplifiers 222 to process bipolar signals from a plurality of ECG and EGM monitoring units 224. The EP console 214 can also include a dedicated AC input filter 234, a AC/DC power supply 236, and a DC/DC power supply 238 to condition and transform mains 120/240 V, 50/60 Hz source power 240 into DC power for use by the diagnostic equipment. ECG and EGM electrode inputs 232 can enter the EP console 214 through a yoke 226 that provides additional input impedance for protection. Junction boxes (1 and 2) 228, 230 can provide convenient plug-in interfaces for IC catheter inputs (not shown) for subsequent processing by EGM monitoring units 224.

FIG. 3 is a block diagram representing a multi-channel analog-to-digital input/output module 300 of the EP hardware system input stage, including an ECG board 302 and an IC board 316, according to some embodiments. The ECG board 302 and the IC board 316 represent a portion of the ECG amplifier 218, unipolar amplifier 220, and bipolar amplifier 222 of FIG. 2. The ECG board 302 and the IC board 316 include a plurality of EP hardware system input stage 400 channels, discussed below (see FIG. 4). FIG. 3 illustrates one (1) 8-channel ECG board and one (1) multi-channel IC board, according to an exemplary embodiment. Some embodiments have at least sixteen (16) channels. Other embodiments can include more or fewer channels.

In FIG. 3, analog inputs V1-V6 304 represent six separate ECG (precordial) electrodes that can be placed at various locations on the patient's chest. Analog inputs LL, RA, and LA 306 represent the left leg, right arm, and left arm limb leads, respectively. Analog output RL 308 represents the patient return line to drive the right leg, as discussed later in this disclosure. WCT 314 on the ECG board 302, also discussed later in this disclosure, represents the Wilson Central Terminal, which also uses the analog inputs II, RA, and LA 306. The output of the WCT 314 can then be input to each channel of the EP hardware system input stage 400 corresponding to the analog inputs V1-V6 304. Each of the digital outputs V1-V6 310 represents a conditioned and digitized version of the respective analog inputs V1-V6 304. In an exemplary embodiment, digital outputs I, 11 312 can include LA referenced to RA as lead I, and LL referenced to RA as lead II, in a conditioned and digitized form. Then, an average of the three limb wires LL, RA, and LA 306 can approximate a zero potential point to provide a reference level for the generation of RL 308.

In FIG. 3, a plurality of analog inputs to the IC board 316 represent possible connections and channels through the EP hardware system input stage 400 (see FIG. 4) from the intracardiac catheters. The IC board 316 can accept IC signals that are either unipolar or bipolar. INDIF 318 represents the indifferent electrode, which provides a reference for a plurality of unipolar indifferent leads. ICUniWCT1, 2, through N signals 320, represent unipolar IC signals referenced to the WCT. ICUniINDIF1, 2, through N signals 322, represent the active electrode of each IC unipolar signal. ICDiff1, 2, through N signals 324, represent a plurality of the bipolar differential signals from IC catheters. A plurality of digital outputs represents the conditioned and digitized versions of the analog inputs, specifically ICUniWCT1, 2, through N signals 326; ICUniINDIF1, 2, through N signals 328; and ICDiff1, 2, through N signals 330.

FIG. 4 is a block diagram representing a single channel of the EP hardware system input stage 400, having circuitry for input protection, signal filtering, detection, feedback, and amplification, according to some embodiments. The circuitry is illustrated in the block diagram by numbered blocks 1 through 11, each representing a part of the functionality of the hardware. This division and labeling of blocks is for ease of description and not meant to limit the scope of protection afforded by the appended claims. The input protection and signal filtering sections of the EP hardware system input stage 400 include symmetric positive and negative circuitry to generate differential versions of each input signal for a differential signal amplification stage 532, described below.

FIG. 5A is a block diagram 500 of the overall EP system disclosed herein, according to some embodiments, generally showing the interface of the Main System Unit (MSU) (hardware components) 504 to the Main Processing Unit (MPU) (software components) 514. FIG. 5A is discussed in more detail later in this disclosure.

FIG. 5B is a block diagram 524 representing the main sections of the EP hardware system input stage 400, with sections 530, 532, 534 cross-referenced to sections shown in the EP hardware system input stage 400.

In FIG. 5B, the analog input protection/filtering stage 530 includes Block 1—Input Protection 402 a, Block 2—RF Filter 404 a, Block 3—Buffer 406 a, Block 4—DC Block 408 a, Block 10—Low Frequency Feedback 420 a, and Block 11—Shield Drive 422 a. The symmetric negative circuitry includes Block 1—Input Protection 402 b, Block 2—RF Filter 404 b, Block 3—Buffer 406 b, Block 4—DC Block 408 b, Block 10—Low Frequency Feedback 420 b, and Block 11—Shield Drive 422h. The signal amplification stage 532 includes differential circuitry that includes Block 5—Instrumentation Amplifier/Filter 410, Block 6—Differential Amplifier 1/Filter 412, Block 7—Differential Amplifier 2/Filter 414, and Block 9—Large Signal Detection/Fast Recovery 418. The A/D converter stage 534 includes Block 8—the A/D Converter 416. The A/D converter stage 534 also includes a communication module 510 (shown in FIG. 5A) that can format the signals for transmission over fiber optic link 512 to the Digital Processing Stage 528, represented in some embodiments by the MPU 514.

The functionality of the specific Blocks 1-11 of FIG. 4, a single channel of the EP hardware system input stage 400, is described in the following paragraphs.

Analog Input Protection/Filtering Stage

The analog input protection/filtering stage 530 of the EP system, shown FIG. 5B, includes Block 1—Input Protection 402 a, 402 b; Block 2—RF Filter 404 a, 404 b; Block 3—Buffer 406 a, 406 b; Block 4—DC Block 408 a, 408 b; Block 10—Low Frequency Feedback 420 a, 420 b; and Block 11—Shield Drive 422 a, 422 b. These elements, according to some embodiments, are described in more detail in the following paragraphs.

Input Protection Circuitry

FIGS. 6A, 7, and 6B illustrate circuits that include the analog input protection/filtering stage 530 of the disclosed EP system, according to some embodiments. FIG. 6A illustrates the overvoltage protection circuitry 600 (represented by Block 1 (402 a, 402 b) in FIG. 4), which can protect the other EP hardware system input stage 400 circuits from large transient voltages, specifically, for example, from defibrillation pulses. The analog input protection/filtering stage 530 can protect against an input voltage that is out of the range of what the circuits can practically handle.

Specifically, the analog input protection/filtering stage 530 can reduce high voltage transients at the ECG, IC, and other electrode lead inputs, which are connected to the patient's body, to less than ten (10) volts, for example, at the inputs to the EP system buffers. The analog input protection/filtering stage 530 can stop a large signal, for example, from a defibrillator, from damaging other portions of the system. In addition, the analog input protection/filtering stage 530 can perform these functions without sinking more than 10%, for example, of the energy of an applied defibrillation pulse, without clamping, or without adding non-linearities when ablation signals are applied.

FIG. 6A illustrates an exemplary embodiment of Block 1's overvoltage protection circuitry 600, including an off-the-shelf gas discharge tube (GDT) 608 that can fire at very high voltages, such as voltages above 300 V, to provide high voltage surge protection. GDT 608 is coupled to two stages of diodes 610, 612 (and resistors 602, 604) designed to sequentially clip the signal to 18 V, for example, to remove a defibrillation signal of up to 5000 V, for example. Diodes 610 represent an off-the-shelf electrostatic discharge (ESD) voltage suppressor device that can aid the GDT 608 until the GDT 608 is fully on. Diodes 612 represent an off-the-shelf bidirectional ESD protection diode that can limit the In2 input of the RF filter (Block 2) to 18 V at the node labeled (a) in FIGS. 6A and 7.

Conventionally, a defibrillation signal of approximately 5000 V would be clamped to +/−5 V to prevent harm. In the case of this disclosure, defibrillation signals can be similarly clamped, but ablation signals with an ablation voltage of approximately 200 V at 500 kHz, for example, can be passed linearly and attenuated by the input resistors RCable, 602, 604 and Block 2 (FIG. 4, 404 a, 404 b), the RF filter 702.

FIG. 7 illustrates an RF filter/shield drive 700, including an RF filter 702 and a shield drive 730. The RF filter/shield drive 700 connects to the overvoltage protection circuitry 600 of FIG. 6A at the node labeled (a) for the transmission of signal In12 through the analog input protection/filtering stage 530. The RF filter 702 of the RF filter/shield drive 700 is described in more detail below. The shield drive 730 of the RF filter/shield drive 700 is also described below.

The input overvoltage protection circuitry 600 does not clamp the ablation signal; rather, the ablation signal is attenuated linearly (e.g., reduced in direct proportion by the input resistors RCable, 602, 604 and RF filter 702) so that it is not inadvertently altered. For example, if the ablation signal is clamped by the input overvoltage protection circuitry 600, there would be no further access to the contents of that signal above the clamping. Advantageously, linear attenuation of the ablation signal by the disclosed EP system can permit recording small cardiac signals of a few millivolts during ablation. A person of ordinary skill in the art will appreciate that the apparatus, systems, and methods disclosed herein apply similarly to other high-frequency signals that may need to be passed through the protection circuit (e.g., not clamped) to prevent generation of non-linearities that would affect the signals of interest.

FIG. 6B represents ESD input protection circuitry 620 at the final section of the analog input protection/filtering stage 530. The ESD input protection circuitry 620 is coupled to the RF filter/shield drive 700 at the node labeled (b) of FIG. 7. An ESD protection chip 622 can provide ESD protection up to 30 kV for data lines and can respond to overvoltage conditions in nanoseconds. Any number of off-the-shelf ESD protection devices can be used for this purpose.

Transient voltage suppressor (TVS) diodes 628, 630 can provide ESD protection exceeding 16 kV by shunting excess current when the induced voltage exceeds their breakdown voltage. TVS diodes 628, 630 can function as “clamping,” or limiting, devices to suppress an overvoltage above their breakdown voltage and can automatically reset when the overvoltage subsides. TVS diodes 622, 630 can also respond to overvoltages faster than other common overvoltage protection components; e.g., “clamping” occurs in about one picosecond. TVS diodes generally can be advantageous for protection against very fast and potentially damaging voltage transients.

FIGS. 8A-8E and 9A-9E illustrate sample signal plots to demonstrate how the front-end input protection circuitry handles high voltage transients and ESD, according to an exemplary embodiment. FIG. 8A illustrates the voltage of a representative defibrillator signal, V(Defib), that is applied to the input of the input protection circuit labeled “EP signals” in FIG. 6A. In a laboratory setting, the defibrillator signal can be derived by applying 5000 volts to a 32 μF capacitor and then discharging the capacitor to the connected electrodes on the patient. Because of inductance and resistance, the amplitude received at the electrodes is approximately 4500 volts lasting some tens of milliseconds.

FIGS. 8B-8E illustrate the different voltage levels as the defibrillation signal proceeds through the circuit. V(In) of FIG. 8B is the voltage on GDT 608 of FIG. 6A. GDTs have very low capacitance (e.g., less than 1 pF) and high impedance (e.g., greater than 100 MOhms) in the off state. They function as a gap between two electrodes. When GDTs ionize and turn on, they may have very low resistance (e.g., a few Ohms) with large current carrying capability (e.g., carrying 10 s of amperes); thus, they act as a short circuit. A disadvantage of GDTs is that they can take some time to turn on, as the plot for V(In) in FIG. 8B shows. GDTs should trigger at 230 V, but the voltage rises to a much higher level before they turn on effectively and start to conduct. Turn-on time can be several hundred nanoseconds. A resistor RCable in FIG. 6A limits the current going into the GDT 608. This can reduce the power that is dissipated in the system and can also ensure that the analog input protection/filtering stage 530 does not shunt any appreciable power meant for the patient.

The ESD voltage suppressor diodes 610 in FIG. 6A can turn on much faster, within a nanosecond, for example, but have a lower power/energy capacity such that they can activate quickly. They can hold the voltage at P1, as shown in the signal plot for V(P1) of FIG. 8C, to around 30 V while the GDT 608 turns on fully. When the GDT 608 is on fully, the ESD voltage suppressor diodes 610 are no longer active.

The next stage in FIG. 6A is a bidirectional pair of ESD protection diodes 612 that can limit the signal at In12, the input to the RF filter (Block 2), to approximately 18 V, as shown in the signal plot for V(In12) of FIG. 8D. The signal through the RF filter is further described below in the RF filter (Block 2) section.

Finally, as shown in FIG. 6B, at In13, after the signal has been filtered by the RF filter of Block 1, an ESD protection chip 622 can clip the signal at VDD +/− a diode drop (e.g., +/−5.7 volts), as shown in the signal plot for V(In13) of FIG. 8E.

A person of ordinary skill in the art will understand that the combination of input protection circuitry shown in FIGS. 6A and 6B, including GDT 608, diodes 610, diodes 612, ESD protection chip 622, and TVS diodes 628, 630, protects the circuitry of an EP recording system. However, this circuitry by itself can be detrimental to achieving a quality EP recording during ablation. For example, if the ablation signals were clipped, the non-linearities produced may cause noise and mask the cardiac signals of interest. Because a medical team may want to see the cardiac signals during ablation, the integration of the Block 2 RF filter with the input protection circuitry is an improvement over conventional solutions. The disclosed embodiments allow unwanted and potentially disruptive or damaging signals to be attenuated while linearly filtering an ablation signal and monitoring ECG and IC signals.

For example, FIGS. 9A-9E are signal plots that illustrate the progression of an ablation signal through the input protection circuit of FIGS. 6A, 7, and 6B. The ablation input is 400 Vpp at the sensor electrodes, as shown by plot V(Defib) in FIG. 9A. As the signal progresses through the stages of the input protection circuit, the signal is attenuated by the resistor RCable (shown as FIG. 9B plot V(In)), resistor 602 (shown as FIG. 9C plot V(P1)), resistor 604 (shown as FIG. 9D plot V(In12)), and capacitor 716 (shown as FIG. 9E plot V(In13)). The ablation signal voltage levels are 100 Vpp at node In of FIG. 6A, 12 Vpp at node In12 of FIG. 6A, and 60 mV at node In13, after the RF filter of FIG. 7. The ablation signal does not trigger the protection devices, but is attenuated linearly, permitting observation and/or recording of the cardiac signals during ablation. The ablation signal can be further filtered at each of the Block 5, 6, and 7 of the signal amplification stage 532 (see FIGS. 4, 5B, and FIG. 10), and at the A/D converter (Block 8 in FIG. 4) that has a 100 dB low-pass filter at 950 Hz.

RF Filter Circuitry with Low-Frequency Feedback and Shield Drive

In addition to its contribution to the input protection circuity to filter and linearly attenuate ablation signals at the EP system input, RF filter 702 can function in concert with the low-frequency feedback circuit of Block 10 (see FIG. 4, 420 a and 420 b, and FIG. 16, 1600) to enable the overall circuit to continue linear attenuation of ablation signals (e.g., with voltage amplitude of about 200 V in the frequency range of about 300 kHz to about 600 kHz) during cardiac monitoring, in near real-time, while passing small cardiac signals (e.g., having a frequency range of about 0.01 Hz to about 500 Hz), for example.

The RF filter 702 can be designed to linearly attenuate the amplitude of the ablation signal by at least 75% in some embodiments, or even by at least 90% in other embodiments, for example. The RF filter 702 can be designed to provide substantially no attenuation to an input signal having a frequency less than 5 kHz, for example. This RF filter 702 can also function in concert with the shield drive 730 of Block 11 (see FIG. 4, 422 a and 422 b, and FIG. 7), which can work with input capacitors 706, 714, 716 of RF filter 702 to help maintain high input impedance of the overall circuit. This high input impedance can help minimize the input losses of the cardiac signal of interest. The shield drive 730 is further discussed below.

Low-Frequency Feedback Circuit

Block 10 (see FIG. 4, 420 a and 420 b), a low-frequency feedback circuit 1600, can provide positive feedback to the Block 2 RF filter (see FIG. 4, 404 a and 404 b, and FIG. 7, 702) to increase input impedance to the EP system, thus reducing signal attenuation. This is advantageous because the input impedance of the EP system in the frequency range of the cardiac signals can be compromised by the RF filter 702.

Specifically, high input impedance at the instrumentation amplifier 1001 of FIG. 10 can be greatly reduced depending on the frequency of the input signal (e.g., by a factor of 100 at 60 Hz) by the presence of the RLC network elements 706, 708, 714, 716 of the RF filter 702. Although the RF filter 702 is advantageous at ablation frequencies, reduction of impedance at low frequencies can reduce the amplitude of the cardiac signals and affect common mode rejection. Without mitigating the effect of the RF filter 702, the advantages of the instrumentation amplifier 1001 would otherwise be lost.

To mitigate that loss and maintain high common mode rejection (e.g., on the order of 100 dB), it is desirable to maintain high impedances at the power line frequencies so that variations in source impedance do not convert common mode signals into differential signals. The Block 10 low-frequency feedback circuit 1600 illustrated in FIG. 16 receives the buffered version of the signal of interest from the Block 3 buffer 406 a, 406 b as Buf1 1602. The low-frequency feedback circuit 1600 then applies operational amplifier 1606 to drive Shield1 728 at the base (that is, bottom plate) of the capacitors 706, 714, 716 in RF filter 702. Specifically, the operational amplifier 1606 serves as a driver to eliminate loading effects and maintain the high input impedance of the analog input protection/filtering stage 530 into the signal amplification stage 532.

When the Block 10 low-frequency feedback circuit 1600 drives the RF filter 702 at low frequencies, there is little or no voltage variation across the capacitors 714, 716. Thus, at low frequencies, capacitors 706, 714, 716 act as open circuits and the high input impedance is maintained. But at higher frequencies, the feedback from the Block 10 low-frequency feedback circuit 1600 is reduced due to the low-pass filtering functionality of Block 10.

Specifically, the combination of a capacitor 1666 and a resistor 1693 at the inverting input to the operational amplifier 1606 filters high frequencies. The output of this circuit no longer tracks the input and holds the Shield1 728 (also the reference node of the RF filter 702) to a fixed level with respect to high frequency signals. This enables the RF filter's 702 passive RLC network 706, 708, 710, 712, 714, 716 to attenuate the high frequency signals.

Specifically, the Block 10 low-frequency feedback circuit 1600 (see also FIG. 4, 420 a and 420 b) takes the buffered signal from the Block 3 Buffer circuit (see FIG. 4, 406 a and 406 b) and produces a correcting signal to Shield1 728 of FIG. 7, that is, the equivalent of the input as a feedback signal at the capacitors 706, 714, 716 of the Block 2 (see FIG. 4, 404 a and 404 b) RF filter 702. This feedback to the capacitors 706, 714, 716 is provided as a dynamic current source for the circuit.

The RF filter 702 of Block 2 404 a, 404 b is enabled for filtering at high frequencies, but the RF filter 702 is disabled at low frequencies when receiving feedback from the low-frequency feedback circuit 1600 of Block 10 420 a, 420 b. At high frequencies, the capacitors 706, 714, 716 in the RF filter 702 function as shunting capacitors that effectively short circuit signals at RF frequencies. The impedance of the capacitors 706, 714, 716 decreases linearly as the frequency becomes higher. The low-frequency feedback circuit 1600 does not affect the EP system at high frequencies.

At low frequencies, the low-frequency feedback correcting signal, Shield1 728 from Block 10 (see FIG. 16) to Block 11 (shield drive 730 of FIG. 7), drives the bottom plates of the capacitors 706, 714, 716, such that these capacitors mimic the input signal. This controls the reference node of the RF filter 702. Specifically, the voltage at the plates of the capacitors 706, 714, 716 vary in sync with each other, and the low-frequency feedback circuit 1600 drives the bottom plate of the capacitors 706, 714, 716 of the RE filter 702 to be the same voltage as the upper plate, such that the voltage difference at the plates of the capacitors 706, 714, 716 becomes zero and the capacitors 706, 714, 716 act as open circuits.

The goal of the low-frequency feedback is to drive the difference between Shield1 728 and Buf1 1602 to zero, such that Shield1 728 equals Buf1 1602. When this occurs, input capacitance can be eliminated. At high frequencies, the positive feedback from operational amplifier 1606 is reduced to zero. In addition, at high frequencies capacitor 722 (which is 30 times larger than other capacitors in the circuit, for example) acts as a short circuit between Shield1 728 and ground. This effectively grounds the reference node of the RF filter 702, fully enabling it to attenuate RF frequencies. Thus, the Block 10 low-frequency feedback circuit 1600 works in concert with a unique arrangement of the Block 2 RF filter 702 elements to remove the loading effect of the RF filter 702 before passing signals to the Block 5 instrumentation amplifier 1001.

In this manner, the instrumentation amplifier 1001 can condition cardiac signals without the overlying ablation signal. The result is that the input to the overall circuit at low frequencies still sees a very high input impedance (e.g., on the order of 10 s of MOhms) that is advantageous to visualizing high-fidelity cardiac signals in an EP environment. Additionally, Block 10 is a symmetric (e.g., mirrored) circuit, so that common mode noise is subtracted as the signal propagates through the circuit. Another advantage of the low-frequency feedback circuit 1600 is that its output Shield1 728 can be used to drive the outer shields of the input cables, for example, at OutS1 of the shield drive 730 of FIG. 7.

Shield Drive Circuit

Block 11 (see FIG. 4, 422 a and 422 b), specifically the shield drive 730, shown in FIG. 7, receives the output of the low-frequency feedback circuit 1600 (Shield1 728 of FIG. 16) of Block 10 (see FIG. 4, 420 a and 420 b) and provides positive feedback to the cable shields at OutS1, thus reducing the effective input capacitance of the input cables. Therefore, the path from the bottom plate of the input capacitors 714, 716 in the RF filter 702 of Block 2 (see FIG. 4, 404 a and 404 b), to the shields of the input cables, further contributes to making the input impedance as large as possible. This high input impedance minimizes the input losses of the cardiac signal of interest. In some embodiments, the shield drive connections are grounded if a shield drive is not desired.

Signal, Buffering and DC Blocking Circuitry

Block 3 (see FIG. 4, 406 a and 406 b) is a low-noise unity gain driver that aids in minimizing the input losses of cardiac signals. Specifically, it can provide the high input impedance to minimize the load of the input stage to the cardiac signals and to drive the signal amplification stage 532. In Block 3, two operational amplifiers (circuit not shown) form two buffers that serve as a unity gain follower that buffers the input and gives the input a high input impedance.

Block 4, the DC Block (see FIG. 4, 408 a and 408 b), is a high-pass module (circuit not shown) that prevents input offsets from the sensor/tissue interface of the patient's body from entering the amplifier gain stages. In Block 4, two DC blocking capacitors (not shown) immunize the input from the large offsets from catheters.

Signal Amplification Stage

The signal amplification stage 532 (see FIG. 5B) of the EP system includes differential circuitry: Block 5—Instrumentation Amplifier/Filter 410, Block 6—Differential Amplifier 1/Filter 412, Block 7—Differential Amplifier 2/Filter 414, and Block 9—Large Signal Detection/Fast Recovery Circuit 418. These circuits are described in more detail in the following paragraphs.

Instrumentation Amplifier/Filter Circuitry

Block 5 (see FIG. 4, 410) is an instrumentation amplifier/filter that provides amplification to the differential signal and common mode rejection of unwanted signals, specifically, power line noise and related harmonics, from the equipment laboratory or medical environment. Block 5, detailed in FIG. 10, has a gain stage 1001 with a differential gain of about 20 at its output, and it provides additional filtering for RF attenuation through its RC network 1008, 1010, 1012, 1014. Two operational amplifiers 1006, 1016, for example, are low-noise devices, designed to receive cardiac signals at the input to the instrumentation amplifier 1001, before the cardiac signals have been amplified. The differential signal from the Block 5 instrumentation amplifier 1001 then enters the precision resistor block 1018 of the Block 6 differential amplifier #1 1017.

Differential Amplifier/Filter Circuitry

Block 6 (see FIG. 4, 412) has a differential amplifier 1020 that produces a fully differential output with a unity gain, as referenced to common mode voltage. Block 6 differential amplifier #1 1017 can provide additional filtering for RF attenuation. Maintaining a fully differential signal path helps reduce noise from entering from the digital part of the system. Such noise would appear mainly as common mode noise and get rejected. This part of the signal amplification stage 532 also shifts the DC bias of the cardiac signal from 0 up to 2.5 V and limits its output from 0 to 5 V.

At an output of Block 6, having a first fully differential amplifier 1020 referenced to common mode, the common mode level is set to 2.5 V as the signals enter Block 7 differential amplifier #2 1021. The circuit continues the low-pass filtering of the ablation signal to the outputs (B2OutP, B2OutN) of Block 7. Block 7, having a second fully differential amplifier 1034 similar to Block 6's differential amplifier 1020, has a gain of about 0.5, with additional filtering for RF attenuation provided by circuit elements 1022, 1024, 1026, 1028, 1030, 1032, 1036, 1038, 1040, 1042. This part of the signal amplification stage 532 maintains the fully differential signal path to continue rejection of noise.

The gain introduced by Block 7 allows the circuit to clip the signal at the input limits of the A/D converter, Block 8 (see FIG. 4, 416), which can be a delta-sigma converter (not shown), for example. As previously mentioned, the Block 6 differential amplifier #1 1017 clips each output signal to 2.5 volts relative to the bias level of 2.5 volts. With gain of 0.5, the outputs of the Block 7 differential amplifier #2 1021 produce signals biased at 2.5 volts with a range of +/−1.25 volts for each output, or 2.5 volts peak-to-peak differential. This represents the limits of a 24-bit A/D converter 416, for example, in some embodiments. By clipping and matching the output limits, the input of the A/D converter 416 is prevented from being overdriven. Because a delta-sigma converter can behave erratically when overdriven, potentially causing spurious results, it is advantageous that the embodiments allow the full range of inputs to the A/D converter, but no more.

The overall gain of the signal amplification stage 532 of the disclosed EP system can be less than or equal to 20 in some embodiments, or can be less than or equal to 50 in other embodiments, for example. For example, in some embodiments, a gain of about 20 at the output of the instrumentation amplifier 1001, a unity gain at the output of differential amplifier #1 1017, and a gain of about 0.5 at the output of differential amplifier #2 1021 produce a system gain of about 10 at the inputs of the A/D converter 416. Generally, the signal amplification stage 532 can include an instrumentation amplifier 1001 with a gain greater than one (1) at its output, a differential amplifier #1 1017 with a gain of about one (1) at its output, and a differential amplifier #2 1021 with a gain of less than one (1) at its output.

The overall low gain of the system, due to its improved ability to remove noise, provides further improvement over conventional systems. Conventional systems that have a 16-bit A/D converter require high gain in order to visualize small signals that are obscured in the presence of higher-amplitude signals. Conventional systems can have gain of up to 5000, for example, causing saturation of signals to occur quickly. Further, if lower gain is used with a 16-bit converter, quantization noise can adversely affect the output results. With the disclosed system having a low gain of about 10, coupled to a 24-bit A/D converter, saturation is prevented until at least 250 mV, for example, of small-signal input, and quantization noise is avoided.

Large-Signal Detection/Fast Recovery Circuitry

The outputs from the Block 6 differential amplifier #1 1017, in addition to being passed to the Block 7 differential amplifier #2 1021, also are passed to Block 9 (see FIG. 4, 418 and FIG. 10), the large-signal detection/fast recovery circuit 1100 of FIG. 11. The large-signal detection/fast recovery circuit 1100 can remove large signals and recover quickly from large transients. This circuit is thus called a “fast recovery” circuit because of its improved ability to recover from saturation much faster than conventionally achieved.

Specifically, the large-signal detection/fast recovery circuit 1100 can detect that the differential input signal has been in excess of 100 mV, for example, for a duration of at least 10 milliseconds, which is identified as an abnormal operating range. On detection of this state, the large-signal detection/fast recovery circuit 1100 can reduce the time constant after the Block 4 DC blocking stage (see FIG. 4, 408 a and 408 b) to ensure that the cardiac signal does not remain in saturation. But, the large-signal detection/fast recovery circuit 1100 can have negligible effect under normal operation. For example, the large-signal detection/fast recovery circuit 1100 can have no effect on fast transients produced by pacing, which can be a signal of interest to monitor and record in an EP environment, and which can have transients that last generally less than 10 milliseconds.

In an embodiment, the first stage of the large-signal detection/fast recovery circuit 1100 has two operational amplifiers 1108, 1112, for example. The gain of the operational amplifier 1108 (e.g., about 40) determines the activation threshold, that is, at which signal amplitude the large-signal detection/fast recovery circuit 1100 can operate to limit (or “soft clamp”) a signal. The activation threshold determines how large the signal must be before the large-signal detection/fast recovery circuit 1100 becomes active and begins to pull the voltages at nodes In14 and In24 toward the common mode level. For example, operational amplifier 1108, with a gain of about 80, can activate the large-signal detection/fast recovery circuit 1100 at about 50 mV; with a gain of about 40, can activate the large-signal detection/fast recovery circuit 1100 at about 100 mV; and with a gain of about 20, can activate the large-signal detection/fast recovery circuit 1100 at about 200 mV. When the signal amplitude reaches the set amplitude level determined by the gain, the voltage will be enough to overcome the activation threshold of a first pair of diode stages 1114, 1116 to activate the large-signal detection/fast recovery circuit 1100.

Operational amplifier 1112 produces a unity gain to buffer the common mode (CM) signal, which provides a common mode reference for the signals through operational amplifier 1108. Operational amplifier 1108 receives U4Out1 and U4Out2 signals from Block 6 (see FIG. 10). Accordingly, the average of the U4Out1 and U4Out2 signals is referenced to the common mode node (CMB of FIG. 11). The signals out of operational amplifier 1108 pass through the first pair of diode stages 1114, 1116 that limit the charging of the subsequent capacitors 1120, 1124, 1128, 1132. These capacitors 1120, 1124, 1128, 1132, which accumulate a charge from the buffered U4Out1 and U4Out2 signals, produce the maximum positive (+) and negative (−) charges for both the inverting and non-inverting version of signals U4Out1 and U4Out2.

The capacitors 1120, 1124, 1128, 1132 form an RC network at nodes C, D, E, and F with resistors 1118, 1122, 1126, 1130, which together serves as a timing network that determines a time constant. The time constant determines how long the signals can be at their maximum amplitude before the large-signal detection/fast recovery circuit 1100 pulls the voltages at nodes In14 and In24 toward CM. This RC network is hereinafter referred to as “timing banks” 1158. Some embodiments of the timing banks 1158 may be designed to produce a time constant of at least 10 milliseconds, for example, to prevent activation of the large-signal detection/fast recovery circuit 1100 during pacing signals of 2-milliseconds to 10-milliseconds duration, for example. Other embodiments may be designed to produce a time constant of at least five (5) milliseconds.

When the capacitors 1120, 1124, 1128, 1132 charge up, a difference is detected, and the signal passes through a second pair of diode stages 1146, 1148, which limits (or “soft clamps”) the input to between about +/−100 mV, for example. This prevents the system from saturating for any appreciable amount of time (e.g., less than 100 milliseconds). The second pair of diode stages 1146, 1148 also ensures that there is no interaction between the large-signal detection/fast recovery circuit 1100 and the EP system if a signal is not large/long enough to require limiting. In other words, when it is not advantageous to activate the large-signal detection/fast recovery circuit 1100, the second pair of diode stages 1146, 1148 disconnects the large-signal detection/fast recovery circuit 1100. The Block 9 large-signal detection/fast recovery circuit 1100 ensures that the EP system is not affected by large signal spikes, and allows a steady-state response where the difference between the inverting and non-inverting U4Out1 and U4Out2 signals is about 100 mV, for example, where operational amplifier 1108 has a gain of about 40, for example.

The Block 9 large-signal detection/fast recovery circuit 1100 is situated in the EP system at a location to remove a large-signal voltage offset. A person of ordinary skill in the art will appreciate that the large signal detection/fast recovery circuit 1100 could be located elsewhere in the EP system where potential large signal spikes may occur and are unwanted. A person of ordinary skill in the art will also appreciate that electronic components, such as the capacitors 1120, 1124, 1128, 1132 and the resistors 1118, 1122, 1126, 1130 of the timing banks 1158, can be substituted within the large signal detection/fast recovery circuit 1100 to change circuit activation levels and times. The large-signal detection/fast recovery circuit 1100 can be used in various embodiments of other signal acquisition and processing systems to remove a large-signal voltage offset from other types of electrical signals, as would be appreciated by a personal of ordinary skill in the art.

In some embodiments, the outputs In14, In24 of the Block 9 large-signal detection/fast recovery circuit 1100 (see FIG. 4, 418) are fed back into Block 4, the DC Block (see FIG. 4. 408 a and 408 b). The DC blocking capacitors of Block 4 (not shown) add an additional bias (e.g., a correcting bias) back to the input signals. Accordingly, a signal from the Block 9 large-signal detection/fast recovery circuit 1100 is not fed back into the Block 4 DC Block unless the signal fed into Block 9 is large (e.g., with an amplitude on the order of 100 mV or greater). In other words, the output signal of Block 9 does not pass into Block 4 unless a large signal event occurs. Nodes In14 and In24 are normally disconnected.

The exemplary embodiment of the large-signal detection/fast recovery circuit 1100 of FIG. 11 is described in detail relative to the signal plots of FIGS. 12, 13A-13C, 14A-14D, and 15A-15B. A sample signal is applied at the inputs to the EP system, and described at various points through the circuit. In this example, the signals shown to demonstrate the large-signal detection/fast recovery circuit 1100 are generated by applying a 20 mVpp signal at node In12 of FIG. 6A and FIG. 7, and zero input at node In22 (the symmetric negative node, not shown), specifically, the inputs to the RF filter 702. At time 10 msec, a 200 mV step is added to the signal at node In12. This becomes a 200 mV differential signal as it traverses through the EP system, which can make the signal move out of the display range of most conventional monitoring devices. Such 200 mV signals should generally be removed so that the signals can be viewed in an EP environment.

FIG. 12 illustrates what happens to such an input signal if the large-signal detection/fast recovery circuit 1100 is not connected. After the sample input 20 mVpp signal with an unwanted 200 mV step-up gets through the analog input protection/filtering stage 530, instrumentation amplifier 1001, and differential amplifier #1 1017 to reach the large-signal detection/fast recovery circuit 1100, if the large-signal detection/fast recovery circuit 1100 is not connected, the EP hardware system cannot recover quickly from the 200 mV step signal. Such slow recovery complicates the identification of cardiac signals.

Resistors 1002 and 1004, located before the instrumentation amplifier 1001 of FIG. 10, pull the offset signals back to a ground level eventually, but a time constant of about 2.7 seconds is produced by the product of the DC blocking capacitor (not shown) of Block 4 and resistor 1002. This introduced delay is too long to recover an off-screen or saturated signal. FIG. 12 illustrates that the signal on the input node In14 moves down inappreciably in about 100 msec and only a few millivolts in about 400 msec (not shown). Such a large-transient signal will likely have an adverse impact on the operation of the EP system without the large-signal detection/fast recovery circuit 1100, because the large transient would push the monitored signal to saturation and the waveform details of the signal would be lost.

FIGS. 13A-13C illustrate the same 200 mV large-transient signal when using a connected large-signal detection/fast recovery circuit 1100. In this example, as shown in FIGS. 13A and 13B, both input nodes of the large-signal detection/fast recovery circuit 1100, In14 and In24 (shown in FIG. 11), are pulled (biased) toward the common mode signal V(CMB), which is at an amplitude of about 100 mV (see FIG. 13C). In14, the positive input node of the large-signal detection/fast recovery circuit 1100, is pulled down, and In24, the negative input node of the large-signal detection/fast recovery circuit 1100, is pulled up. V(CMB) is the average of the voltage at nodes In14 and In22 (the symmetric negative input to the overall circuit). The actual common mode level of nodes In14 and In24 has no impact because the desired bias level is applied directly to the differential amplifiers of Blocks 6 and 7 (1020 and 1034, respectively), which sets the common mode voltage at those differential amplifiers 1020, 1034.

The plots in FIGS. 13A and 13B illustrate that the voltages of nodes In14 and In24 are pulled into monitoring range after about 50 milliseconds. The limiting, or “soft clamping,” is thus performed gradually to avoid discontinuity in the signal acquisition and visualization. Other embodiments may allow for a gradual “clamping” in about 100 milliseconds.

FIGS. 14A-14B demonstrate how a large-transient signal is conditioned as it traverses the various internal nodes of the large-signal detection/fast recovery circuit 1100. Signal plots V(A) of FIG. 14A and V(B) of FIG. 14B represent the outputs of the operational amplifier 1108 of the large-signal detection/fast recovery circuit 1100 in FIG. 11. In this example, operational amplifier 1108 has a gain of about 40, relative to the input, and produces a (40×200 mV=) 8-volt differential signal across nodes A and B in FIG. 11.

As shown in plot V(C) of FIG. 14C, following node B of FIG. 11, the negative signal pulls down the voltage at node C of FIG. 11. Here, the signal has been filtered to remove the in-band signal that occurs at node B, leaving a low-frequency control voltage at node C. The negative voltage at node C is connected to In14 through resistor 1140, diode 1150, and resistor 1144. This produces a current that pulls In14 down toward the common mode voltage, such as illustrated in FIG. 13A. Similarly, as shown in plot V(E) of FIG. 14D, node A pulls up In24 toward the common mode voltage through node E and J of FIG. 11.

The diodes in the large-signal detection/fast recovery circuit 1100 of FIG. 11 control the direction of current flow. The first pair of diode stages 1114, 1116 (limiting diodes) allows different time constants for charging and discharging nodes C, D, E, and F. They also provide a non-operating range where the nodes C, D, E, and F are not charged when the outputs A and B are less than the diode forward voltage drop. The “clamping” diodes 1150, 1152, 1154, 1156 of the second pair of diode stages 1146, 1148 ensure that input nodes In14 and In24 are pulled in the correct direction.

FIGS. 15A-15B show signal plots of the current through the resistors 1144, 1142 at the outputs In14 and In24, respectively, of the large-signal detection/fast recovery circuit 1100 of FIG. 11. During normal operation, the current is 0 and the instrumentation amplifier/filter 410 circuit is unaffected. When the differential level is too high (that is, when a large signal is detected, for example, in excess of 100 mV over several milliseconds), the current in those two resistors 1144, 1142 help pull the signals hack toward the common mode voltage, V(CMB).

A/D Converter

The A/D Converter 416, Block 8 (see FIG. 4), is a fully differential A/D converter that is designed to accept differential signals from the rest of the circuit. In some embodiments, each of the EP system circuit modules is duplicated eight times so to feed as differential pairs into the eight separate channels of the A/D Converter 416. A TI ADS1278 24-bit, 8-channel delta-sigma converter can be used, for example. A person of ordinary skill in the art may choose other A/D converters of similar specifications.

in some embodiments, the A/D converter 416 is highly linear, a characteristic of delta-sigma converters. The high linearity allows accurate digital signal processing to be performed in the software, as described below. This configuration minimizes hardware filtering to that advantageous for RF attenuation and anti-aliasing, and allows more flexibility of filtering and signal processing in software. The advantage of choosing a fully differential A/D converter is that common mode noise signals from any digital circuitry (e.g., a digital clock signal) are rejected.

Wilson Central Terminal-Right Leg Drive (WCT-RLD) Circuit

Although input common mode signals can be at any frequency, the dominant signals are generally at the power line frequency: 60 Hz in the U.S., for example. In a conventional EP environment, ECG (and similar) equipment mitigates a large amount of 60 Hz noise that could be up to 100 times larger than the signal of interest. In addition, because of distortions in the power line signal, there is often a strong third harmonic at 180 Hz, which is generally the noisiest harmonic. Higher harmonics and other common mode signals are generally smaller and/or are above the frequency band of interest for the ECG and IC signals.

In some embodiments, a Wilson Central Terminal-Right Leg Drive (WCT-RLD) circuit is used to remove particularly the 60 Hz and 180 Hz noise by common mode rejection, that is, by enhancing the first and third harmonic frequencies of the power line signals and selectively feeding those signals back to the patient to cancel them out. FIG. 23 illustrates a schematic diagram of an improved WCT-RLD circuit, according to some embodiments.

For example, a WCT circuit 2332 of FIG. 23 provides a virtual ground by summing and averaging two or three limb electrodes (e.g., right arm 2304 and left arm 2306, or the right arm 2304, left arm 2306, and left leg 2308) connected to a central terminal 2336 through two or three large resistors 2334 (e.g., 20 kOhms on each electrode). A person of ordinary skill in the art will understand that the average of the right arm (RA) 2304, left arm (LA) 2306, and left leg 2308 provides a more accurate estimate of the common mode signal on the patient 2302 than does the average of the right arm (RA) 2304 and left arm (LA) 2306. As also understood by a person of ordinary skill in the art, the RA and LA signals are alternatively buffered (see buffer 2312) versions of the RL positive (RLP) 2338 and RL negative (RLN) 2340 signals. A WCT is conventionally designed to reduce the overall 60 Hz common mode noise signal by bringing the net potential difference of these limb leads close to zero.

The addition of an active current via the right leg, the “right leg drive” (RLD) circuit 2330, to the WCT circuit 2332 allows the patient 2302 to be driven to the same voltage as the common amplifier, thus reducing the common mode voltage at the inputs of the ECG electrodes (LA, RA, LL, and V1 to V6). This can be done by generating the inverse of the common mode signal and applying that as an output to the right leg. Specifically, the right leg drive is represented by limb electrode RL. The patient 2302 receives, through the RL electrode, an RLD output 2310, a summed and inverted version of the other IC catheter signals or ECG electrode signals, canceling interference present in the patient's body. This, in combination with the common mode rejection properties of the signal amplification stage 532, can reduce common mode low-frequency interference to acceptable levels (specified by standard IEC 60601-2-25, for example).

However, because 60 Hz and 180 Hz noise is not equal in all parts of the body, common mode rejection alone cannot remove all of the noise. The WCT-RLD circuit 2300 of FIG. 23 provides a reference signal, approximately equal to the line frequency coming into the system, which further reduces the overall common anode signal. Thus, the combination of the disclosed WCT-RLD circuit 2300 and conventional common mode rejection provides an advantageous improvement in the reduction of the common mode signal.

In an exemplary embodiment using the WCT, the WCT input within the EP system can provide an optional unipolar input to replace the bipolar positive (+) or negative (−) catheter input to the Block 3 Buffer circuit (see FIG. 4, 406 a and 406 b). Specifically, the WCT-RLD circuit 2300 averages the right arm 2304, left arm 2306, and left leg 2308 electrode signals. The result is buffered by the operational amplifier 2314, and the output WCTBuf 2316 is sent as a unipolar feedback signal wherever it is desired in the EP system, specifically used in embodiments whenever a patient is connected. The WCT-RLD disclosed herein enhances a conventional unipolar WCT solution with a novel approach for generating an RLD signal.

In some embodiments, a novel approach in the WCT-RID circuit 2300 is to provide additional filter circuitry, called a “Twin-T” feedback network 2440 (see FIGS. 23 and 24), which can produce a stronger RLD at the 60 Hz power line frequency or at the 180 Hz third harmonic frequency. This is specifically helpful during ablation. The Twin-T feedback network 2440 resonates at both 60 Hz and 180 Hz, but advantageously prevents phase oscillations by reducing feedback at other frequencies.

FIG. 24 illustrates a schematic diagram of a Twin-T feedback network 2440 interfaced with the RLD circuit 2330 of the SWT-RLD circuit 2300, according to some embodiments. The Twin-T feedback network 2440 of FIG. 24 serves as an improved notch filter. Resistors 2406, 2407, 2408, 2409, 2410, 2411, and capacitors 2401, 2402, 2403, 2404 form a single Twin-T network that generates a notch at 60 Hz. The next stage, resistors 2412, 2413, 2414, 2417, 2418, 2419, and capacitors 241.5, 2416, 2420, 2421, similarly generates a notch at 180 Hz. However, when the network is in an operational amplifier feedback path, the inverse function is obtained.

For example, as illustrated in the plot 2500 of FIG. 25, the RLD output of the Twin-T feedback network 2440 at operational amplifier 2425 produces two peaks, one at 60 Hz 2510 and one at 180 Hz 2520. At higher frequencies, such as 10 kHz or greater, the phase change approaches zero. This prevents phase changes in the RLD circuit 2330 at these higher frequencies that can cause oscillation. Minimal phase changes at these higher frequencies can prevent oscillations near the ablation frequencies, which would otherwise be more difficult to filter out.

Although Twin-T circuitry is used in electronic design, it has not been previously used in a WCT-RLD circuit as disclosed herein. The Twin-T feedback network 2440 removes power line signals conventionally passed by known circuits when generating a RLD signal, such that the power line signals do not affect phase response at higher frequencies. The Twin-T feedback network 2440 thus has an advantageous use for generating a RLD signal from electrode leads.

In the embodiment of FIG. 23, the RLD circuit 2330 follows the power line by feeding the RLD output 2310 as a separate signal back into the patient 2302. In the circuit, the right leg positive (+) (RLP) 2338 and right leg negative (−) (RLN) 2340 differential input signals, which can alternatively be the RA and LA signals, are buffered 2312. Then, the Twin-T feedback network 2440 emphasizes/amplifies the buffered right leg signal at 60 Hz and 180 Hz, which is inverted and buffered again by the RLD circuit 2330. This RLD circuit 2330 includes an operational amplifier 2328, resistors 2320, 2324, 2326, and capacitors 2318, 2322. After passing through the RLD circuit 2330, the signal is output as the RLD output 2310 (RLDrv) at a surface lead on the patient's right leg. The effect is that the entire circuit tracks the power line, and the common mode of the circuit rejects the power line noise. Additionally, the circuit of the right leg drive protects against any signal going back into the patient that is greater than approximately one (1) microampere.

In some embodiments, using first-order derivatives of both unipolar signals allows a physician to know whether a signal of interest is arising from the distal or proximal electrode. The bipolar signals can be displayed in a color-coded format to identify which components in the bipolar signals arise from the cathode versus which arise from the anode. The physician can then manually move to the proximal electrode if the main signal of interest arises from there. The system can also be automated in conjunction with robotic systems to make the move as part of a closed feedback loop.

Case Examples

The following cases illustrate how the disclosed hardware circuitry conditions signals found in an EP environment, allowing improved cardiac monitoring in the midst of equipment and environment noise, and during procedures that introduce large, potentially interfering signals into the monitoring environment.

Signal Case #1—Common Mode 60 Hz and In-Band 500 Hz Differential Signal

Signal case #1 presents a typical common mode 60 Hz noise signal with an in-band (less than 1000 Hz) differential signal as found from conventional IC leads. In this example, a series of signal plots representing the signal at exemplary nodes of the disclosed circuit is shown. The circuit amplifies the differential signal and rejects the common mode signal.

FIGS. 17A-17B illustrate an input signal of 2 Vpp 60 Hz sine (power line) signal applied to input nodes In12 (see FIG. 6A) and In22 (the negative, lower branch of the circuit, not shown), respectively. Superimposed on In12 is a 0.2 Vpp, 500 Hz sine wave signal (see plot V(In12) of FIG. 17A) and on In22 is a −0.2 V, 500 Hz sine wave signal (see plot V(In22) of FIG. 17B). This results in a 2 Vpp, 60 Hz common mode signal and a 0.4 V, 500 Hz differential signal. These signals may be too low in frequency to be affected by the RF filter 702 of Block 2, so the same signals appear at the output of Block 3 (Buffer 406 a, 406 b) and after Block 4 (DC Block 408 a, 408 b).

FIGS. 17C-17D illustrate shield input signals (Shield1, Shield2) that are also the same as the corresponding input signals shown in FIGS. 17A-17B. These signals are fed back from Block 10 (low-frequency feedback circuit 1600) to the RF filter 702 to eliminate loading from the RF filter 702. (See Shield1, 728 of FIG. 7. Shield2, the negative, lower branch of the circuit, is not shown.) The voltage change on capacitors 714, 716, 706 of the upper branch of the RF filter 702 in FIG. 7, as well as on the corresponding capacitors on the symmetrical lower branch of the RF filter (not shown) is close to 0, effectively removing them from the circuit at low frequencies.

FIGS. 18A-18B illustrate Out1 and Out2, the outputs of Block 5 (instrumentation amplifier 1001 of FIG. 10) with a differential gain of 20. The common mode signal has a gain of 1 and the differential signals have a gain of 20. The signal at this point becomes a 2 Vpp, 60 Hz sine wave at each output with a superimposed 4 Vpp, 500 Hz signal at Out1 (see FIG. 18A) and a −4 Vpp, 500 Hz signal at Out2 (see FIG. 18B), creating a 8 Vpp differential signal.

FIGS. 18C-18D illustrate the outputs B2OutP and B2OutN of FIG. 10, respectively. At B2OutP and B2OutN, the signals have passed through the fully differential operational amplifiers (Blocks 6 and 7, 1017, 1021) of FIG. 10, have eliminated the common mode signal, and have referred the outputs to the common-mode output voltage, VOCM (2.5V bias level). The gain of 0.5 at amplifier 1034 of Block 7 results in a final set of 500 Hz signals of 2 Vpp at B2OutP (see FIG. 18C) and −2 Vpp at B2OutN (see FIG. 18D), which is equivalent to a 4 Vpp differential 500 Hz signal. From the input to the output, the common mode gain is 0 and the differential gain is 10. The common mode signal can thus be eliminated through the combined responses of the instrumentation amplifier (Block 5) and the fully differential operational amplifiers (Blocks 6 and 7).

Signal Case #2—500 kHz Ablation Signal

Signal case #2 presents a typical 500 kHz ablation signal applied to the EP system inputs during an ablation procedure as cardiac monitoring continues. The unwanted ablation signal is filtered and attenuated before reaching the A/D converter (see FIG. 4, Block 8, 416) of the disclosed circuit.

As seen in FIGS. 19A-19B, the ablation signal input is a 0.2 Vpp, 500 kHz sine wave applied to In12 (FIG. 19A) and −0.2 Vpp, 500 kHz sine applied to In22 (FIG. 19B). This results in a 0.4 V, 500 kHz differential signal. This signal is in the frequency range to be attenuated by the RF filter 702 of Block 2 (FIG. 4, 404 a and 404 b).

FIGS. 19C-19D illustrate plots of the output of the RF filter 702 (Block 2) In13 (and the symmetric lower branch RF filter output 4123) when the circuit receives an ablation signal. The plots V(In13) of FIG. 19C and V(In23) of FIG. 19D are shown at the same scale as the input. The signal can be seen to be attenuated to a few millivolts.

The plots of V(Shield1) and V(Shield2) shown in FIGS. 20A and 20B, respectively, illustrate that the same signals over the shield input (see Shieldl of FIG. 7, for example) are also greatly attenuated, effectively grounding the lower plates of capacitors 714, 716, 706 of the upper branch of the RF filter 702 in FIG. 7, and the corresponding capacitors on the symmetrical lower branch of the RF filter (not shown), to enable the RF filter to attenuate the 500 kHz ablation signal.

FIGS. 21A and 21B illustrate plots of the signals V(Out1) and V(Out2), respectively, at the outputs of the Block 5 (instrumentation amplifier 1001 of FIG. 10), with a gain of 20. The remaining 500 kHz signal goes through this 20× gain stage, but the filtering on this stage (from capacitors 1010 and 1012) limits the gain at 500 kHz to approximately 1×.

As shown in FIGS. 21C-21D, the successive fully differential operational amplifiers 1017, 1021 in Blocks 6 and 7 of FIG. 10 (and their negative, lower branch circuit equivalents) continue to filter the 500 kHz signal until it is less than 0.5 mV at B2OutP (FIG. 21C) and B2OutN (FIG. 21D). The remaining signal is removed by the filter on the Block 8 A/D converter (see FIG. 4, 416), which provides 100 dB attenuation above 1000 Hz. The ablation signal is thus eliminated through the combined responses of the RF filter (Block 2), the instrumentation amplifier (Block 5), and the fully differential operational amplifiers (Blocks 6 and 7).

Hardware/Software Interface

FIG. 5A illustrates the relationship between the hardware and software of the disclosed EP recording system, according to some embodiments. The Main System Unit (MSU) 504 contains the hardware circuitry of the EP recording system. In FIG. SA, the ECG board 506 with WCT 507 corresponds to the ECG board 302 and WCT 314 shown in FIG. 3. (For cross-reference, the ECG board 302, 506 digital signal outputs are V1-V6 310 and I-II 312.) Similarly, the IC board 508 corresponds to the IC board 316 in FIG. 3. (For cross-reference, the IC board 316, 508 digital signal outputs IC1 . . . ICN are ICUniWCT1-ICUMWCT2 326. ICUniINDIF1-ICUniINDIF2 328, and ICDiff1 . . . ICDiffN 330.) To communicate the digital signal outputs from the ECG board 506 and IC board 508 to the software of the Main Processing Unit (MPU) 514, a Communication Module 510, and a fiber optic link 512 are provided.

According to some embodiments, the Communication Module 510 of the MSU 504 transmits the independent digital signals from the A/D converter 416, 534 of the ECG board 506 and IC board 508 to the MPU 514 over a fiber optic link 512 for digital signal processing. The Communication Module 510 samples the output channels from the A/D converter 416, 534, converts them to serial format, and transmits the data over the fiber optic link 512. The signals are converted back to a parallel format at the receiving end of the fiber optic link 512 in the MPU 514.

In this specification, the ECG board 302, 506 and IC board 316, 508 are named thusly for sake of convenience. As would be understood by a person of ordinary skill in the art, the circuitry of the ECG board 302, 506 and IC board 316, 508 can accept other physiologic signals from various types of electrodes other than ECG and IC electrodes.

EP Recording System Software Description

Provided herein are system apparatus, device, method and/or computer program product embodiments, and/or combinations and sub-combinations thereof, for processing and displaying multiple signals in near real-time. For example, the embodiments may involve processing and display multiple biomedical signals (e.g., EP signals) in near real-time. Before describing further details of these embodiments, a brief overview of digital signal processing is provided.

At a high level, digital signal processing is the use of digital processing to identify particular features in a signal, or producing a signal that is of higher quality than the original signal (e.g., by removing noise from the signal). Digital signal processing may be performed on a digitized electrocardiography (ECG) or intracardiac (IC) signal representing the electrical activity of a heart over a period of time.

To perform digital signal processing on an analog signal, the analog signal needs to be converted to digital form. An analog-to-digital (AD) converter such as A/D converter 416 can convert the analog signal to digital form, as is well known to a person of ordinary skill in the art.

Digital signal processing may involve applying a digital signal processing function to one or more signal samples in a sequence of signal samples for a signal. A digital signal processing function can be a sequence of mathematical operations and computational algorithms. A digital signal processing function can measure, filter, compress, or optimize a signal sample, for example.

Digital signal processing can use different digital signal processing functions depending on the type of analysis and the type of signal being processed. For example, digital signal processing can use a different digital signal processing function to identify particular words in a speech signal or to remove motion blur from a video signal.

Digital signal processing systems have many applications such as audio signal processing, audio compression, digital image processing, video compression, speech processing, speech recognition, digital communications, digital synthesizers, radar, sonar, financial signal processing, and seismology. But conventional digital signal processing systems often cannot be used in certain applications such as biomedical signal processing. This is because conventional digital signal processing systems, including current EP solutions, are often unable to simultaneously display multiple signals in near real-time. Moreover, conventional solutions do not enable a user to dynamically apply a new digital signal processing function to a base signal. And, conventional solutions are often unable to synchronize the processing and display of multiple signals in near real-time. This is often problematic in clinical settings because the ability of a physician to make an effective clinical diagnosis may depend on comparing multiple signals at the same point in time. Finally, conventional EP systems that use analog filters are often unable to take full advantage of digital signal processing. This is because when functions are implemented in hardware, the options are greatly restricted. For example, the functions cannot be removed and therefore the full potential of digital signal processing cannot be obtained.

The digital signal processing (DSP) system disclosed herein goes further than to solve the problems of these conventional systems. In addition to using simultaneous multiple DSP filters for processing, time-aligning, and displaying multiple signals in near-real time, the system clarifies operating endpoints for biomedical procedures such as ablation so that an operator's job is more efficient. For example, this disclosure provides high-fidelity surface ECG signals to automate and create a signal-averaged, late-potential electrocardiogram. An ablation procedure uses an internal cardiac map so that the operator can visualize the cardiac tissue for ablation. When the internal cardiac map is created, the adequacy of the map is judged by the percentage map to the surface signal-averaged, late-potential ECG. In other words, if a complete map is created, all the intracardiac signals with late potentials when summed together should reproduce both timing and amplitude of the signal-averaged, late-potential map from the high fidelity ECG. A score is displayed to represent the adequacy of the map. For example, a score of 50% means that the mapping catheter has not reached sites where some of the late signals exist as they must exist to explain the high-fidelity signal-averaged, late-potential map data. Following ablation of late potentials, real-time high-fidelity signal-averaged late-potential ECGs determine whether the abnormal late potentials have indeed been ameliorated. If not, then further ablation of previously tabbed late potentials using the late potential filter and dynamic window for guidance can be performed. The disclosed system provides data to direct an operator to accurate late-potential areas in the map to reduce the need for further ablation.

FIG. 26 is a block diagram of a system 2600 for processing and displaying multiple signals in near real-time, according to some embodiments. System 2600 can represent MPU (Software) 514 in FIG. 5A, and implement digital processing stage 528 of FIG. 5B. System 2600 includes signal path module 2602, configuration path module 2620, and monitoring module 2622. Signal path module 2602, configuration path module 2620, and monitoring module 2622 can be software modules capable of being executed by a processor (or processors) such as processor 8504 in FIG. 85. Alternatively, a plurality of processors can be used.

Signal path module 2602 includes input module 2604, timer 2605, packetizer 2606, queuing module 2608, packet dispatcher 2610, global signals table 2612, and output module 2616. Input module 2604, timer 2605, packetizer 2606, queuing module 2608, packet dispatcher 2610, global signals table 2612, and output module 2616 can be software modules capable of being executed by a processor (or processors) such as processor 5004. Signal path module 2602 solves at least the technological problem of how to synchronize the processing and display of multiple signals in near real-time. Signal path module 2602 solves this technological problem using a novel multistage process involving packetization, queueing, and processing delay equalization, as described below.

In a first stage, input module 2604 can receive signal samples for one or more base signals. A base signal can be a signal before any digital signal processing is applied. For example, a base signal can be a biomedical signal such as an ECG or IC signal. As would be appreciated by a person of ordinary skill in the art, a base signal can be various other types of signals. Input module 2604 can receive signal samples for multiple base signals. For example, input module 2604 can receive signal samples of an IC signal and signal samples of an ECG signal.

Input module 2604 can receive signal samples of a base signal from a hardware device associated with MSU (Hardware) 504 in FIG. 5. For example, input module 2604 can receive signal samples from a hardware device such as EGG board 302 or IC board 316 in FIG. 3. Input module 2604 can also receive signal samples from data stored in a computer file. For example, the computer file can contain previously recorded signal samples received from a hardware device.

Input module 2604 can receive signal samples from a hardware device via A/D converter stage 534. For example, input module 2604 can receive signal samples of a base signal from EGG board 302.

Input module 2604 can receive signal samples of a base signal from an electrode attached to a hardware device. For example, input module 2604 can receive signal samples for each of eight (8) electrodes attached to ECG board 302. As would be appreciated by a person of ordinary skill in the art, input module 2604 can receive more or fewer signal samples depending on the number of hardware devices connected to input module 2604, and the number of electrodes attached to each hardware device.

Input module 2604 can store the one or more signal samples for each base signal in a computer storage device for later analysis by review module 2624. For example, input module 2604 can store the one or more signal samples in main memory 8508 or hard disk drive 8512 in FIG. 85. This enables a user (e.g., a physician) to review the one or more signal samples for each base signal after having been acquired.

Input module 2604 can dispatch the one or more signal samples for each base signal to packetizer 2606. Packetizer 2606 can perform preprocessing on the received signal samples. Packetizer 2606 can perform preprocessing on the received signal samples to ensure that the resulting signal is compatible with later stages in signal path module 2602. As would be appreciated by a person of ordinary skill in the art, the type of preprocessing that packetizer 2606 performs can depend on the type of base signal. For example, packetizer 2606 can convert the binary values of the received signal samples to their corresponding physical values, e.g., for display of the base signal.

After preprocessing the received signal samples, packetizer 2606 can store the one or more signal samples of a base signal into a packet. A packet may be a consecutive sequence of N signal samples belonging to the same base signal. Packetizer 2606's storage of signal samples into packets can enable signal path module 2602 to synchronize the processing and displaying of multiple signals in near real-time, especially on a non-real-time operating system. In other words, a packet is the unit of processing in signal path module 2602.

Packetizer 2606 can store one or more signal samples in a packet based on timer 2605. Timer 2605 can be a high-resolution timer. For example, timer 2605 can be a Microsoft Windows® high-resolution timer having a 1-millisecond resolution. Timer 2605 can be set to an amount of time associated with receiving a fixed number of signal samples (e.g., N signal samples) from a hardware device or from a computer file. The fixed number of signal samples may correspond to the number of signal samples capable of being stored in a packet.

Packetizer 2606 can use timer 2605 to ensure that each packet contains the same number of signal samples. Specifically, packetizer 2606 can set timer 2605 to an amount of time associated with receiving a given number of signal samples of a base signal. In other words, packetizer 2606 can expect to receive a certain number of signal samples when timer 2605 is triggered.

Packetizer 2606 can start timer 2605. Packetizer 2606 can then store signal samples received from input module 2604 into a packet until timer 2605 is triggered. Packetizer can then dispatch the packet to queuing module 2608. Packetizer 2606 can then restart timer 2605. Packetizer 2606 can then store a new set of signal samples received from input module 2604 into a new packet until timer 2605 is triggered again.

Packetizer 2606 can assign a tag to each packet. Packetizer 2606 can assign the same tag to each packet associated with a different base signal for the same period of time. This assignment can enable signal path module 2602 to synchronize the processing and displaying of packets for different base signals for the same period of time. The assigned tag may be used by a display module 2618 to synchronize the output of different signals. In other words, the display module 2618 can work on the same tag at any given time.

The assigned tag can correspond to the time period in which signal samples in the corresponding packet were received. Specifically, the tag can correspond to the sample number of the first signal sample in the corresponding packet. For example, packetizer 2606 can store sixteen (16) signal samples in each packet. In this case, packetizer 2606 can store the first set of signal samples in a packet with a tag of 0. Packetizer 2606 can store the second set of signal samples in a packet with a tag of 15. Packetizer 2606 can store the subsequent sets of signal samples in packets with tags of 31, 47, 64, etc. As would be appreciated by a person of ordinary skill in the art, other tag assignment conventions can be employed.

After packetization, packetizer 2606 can store each generated packet associated with a given base signal in queuing module 2608. Queueing module 2608 is shown in FIG. 27.

FIG. 27 is a block diagram of queuing module 2608 for the storage of each generated packet associated with a different base signal, according to some embodiments. Queueing module 2608 solves at least the technological problem of how to dynamically apply multiple different digital signal processing functions to the same base signal. Queueing module 2608 solves this technological problem by storing generated packets associated with each base signal in separate queues that can be dynamically processed by different signal modules 2614. FIG. 27 is discussed with reference to FIG. 26.

Queuing module 2608 includes one or more queues 2702. For example, in FIG. 27, queuing module 2608 includes queue 2702-1, queue 2702-2, and queue 2702-N. Each queue 2702 can be associated with a given base signal. Queue 2702 can be a queue data structure that stores items in the order they are inserted. For example, the first item inserted into queue 2702 is the first item removed from queue 2702. In other words, queue 2702 is a first-in-first-out (FIFO) data structure. As would be appreciated by a person of ordinary skill in the art, queue 2702 can be implemented using an array, linked list, or various other data structure.

Packetizer 2606 can store each generated packet associated with a given base signal in a corresponding queue 2702. For example, packetizer 2606 can store generated packets associated with an IC signal into queue 2702-1, and generated packets associated with an ECG signal into queue 2702-2.

Packetizer 2606 can store each packet in a queue 2702 in the order generated. This can ensure that the signal samples in the generated packets are processed in the order they are received from the hardware device or from the computer file.

Returning to FIG. 26, packet dispatcher 2610 can dispatch a generated packet from a queue 2702 in FIG. 27 to one or more signal modules 2614 in global signals table 2612 for digital signal processing. Packet dispatcher 2610 solves at least the technological problem of how to dynamically apply multiple different digital signal processing functions to the same base signal. Packet dispatcher 2610 solves this technological problem by dynamically dispatching generated packets associated with each base signal to the appropriate one or more signal modules 2614 for digital signal processing.

Packet dispatcher 2610 can continuously scan the one or more queues 2702 in queuing module 2608. Each time packet dispatcher 2610 detects a new packet available in a queue 2702 in queuing module 2608, packet dispatcher 2610 can remove the new packet from the queue 2702. Packet dispatcher 2610 can then dispatch the new packet to one or more signal modules 2614 in global signal tables 2612 for digital signal processing. Packet dispatcher 2610 can dispatch the same packet to multiple signal modules 2614 so that the base signal can be simultaneously processed using different digital processing functions. Moreover, because packet dispatcher 2610 can dispatch packets from different queues 2702 to different signal modules 2614, different base signals can be simultaneously processed using different digital signal processing functions.

Packet dispatcher 2610 can dispatch a new packet from a queue 2702 to one or more signal modules 2614. Packet dispatcher 2610 can dispatch the new packet to one or more signal modules 2614 using global signals table 2612. Global signals table 2612 can be a fixed size array. Each element of the array can be associated with a given base signal, and thus a given a queue 2702. For example, if there are 100 base signals, global signals table 2612 can be a fixed size array of 100 elements. Moreover, for each element of the array, there can be one or more signal modules 2614 designed to process the corresponding base signal. In some embodiments, each element of the array can be a fixed size array itself Each element of this subarray can be associated with a given signal module 2614. For example, if there are 10 signal modules 2614, this subarray can contain 10 elements. Thus, by way of example and not limitation, global signals table 2612 can be a 100×10 array.

Packet dispatcher 2610 can dispatch the new packet to a signal module 2614 by checking the corresponding element in the subarray associated with the base signal of the new packet. Specifically, packet dispatcher 2610 can determine whether the corresponding element in the subarray indicates that the signal module 2614 is assigned to the base signal associated with the packet.

In some embodiments, global signals table 2612 can indicate whether a given signal module 2614 is assigned to a given base signal by storing a ‘0’ or ‘1’ at the corresponding element in the subarray associated with the given signal module 2614. For example, global signals table 2612 can indicate that the given signal module 2614 is not assigned to the given base signal by storing a ‘0’ at the corresponding element in the subarray. In some other embodiments, global signals table 2612 can indicate whether a given signal module 2614 is assigned to a given base signal by storing a reference to the given signal module 2614 at the corresponding element in the subarray. As would be appreciated by a person of ordinary skill in the art, the reference can be a memory pointer, flag, handle, or other type of identifier.

Packet dispatcher 2610 can also dispatch the new packet to one or more signal modules 2614 using a lookup table. The lookup table may map a given queue 2702 to one or more signal modules 2614. Packet dispatcher 2610 can dynamically determine which one or more signal modules 2614 are associated with a given queue 2702 using the lookup table. Packet dispatcher 2610 can then dispatch the packet to the one or more determined signal modules 2614 for digital signal processing.

Before packet dispatcher 2610 can begin dispatching packets to one or more signal modules 2614 for digital signal processing, configuration path module 2620 can configure signal path module 2602. Configuration path module 2620 can perform this configuration during initialization of system 2600, or when a user applies a new configuration to signal path module 2602. Configuration path module 2620 is shown in FIG. 28.

FIG. 28 is a block diagram of configuration path module 2620 for configuring signal path module 2602 to synchronize the processing and display of multiple signals in near real-time, according to some embodiments. Configuration path module 2620 solves at least the technological problem of how to synchronize the processing and display of multiple signals associated with one or more base signals in near real-time. Configuration path module 2620 solves this technological problem by equalizing the processing delays of each signal module 2614 such that each signal module 2614 completes processing of the same corresponding packet at approximately the same time. FIG. 28 is discussed with reference to FIG. 26.

Configuration path module 2620 includes a signal configuration module 2802, a signal factory module 2804, a digital signal processor (DSP) equalizer 2806, and a DSP factory module 2808. Configuration path module 2620 is a software module capable of being executed by a processor (or processors) such as processor 5004. Configuration path module 2620 controls the execution of signal factory module 2804, DSP equalizer 2806, and DSP factory module 2808. Signal factory module 2804, DSP equalizer 2806, and DSP factory module 2808 can be software modules capable of being executed by a processor (or processors) such as processor 5004.

During initialization of system 2600, or in response to a user applying a new configuration to system 2600, configuration path module 2620 can generate and configure one or more signal modules 2614 in global signals table 2612. In some embodiments, the execution of signal path module 2602 and monitoring module 2622 can be paused during the execution of configuration path module 2620.

Configuration path module 2620 includes signal configuration module 2802. Signal configuration module 2802 can receive one or more signal processing specifications. A signal processing specification can be used to generate and configure a signal module 2614. A signal processing specification may specify a base signal to process, the lengths of input and output packet queues for a signal module 2614, and a digital signal processing function to use to process the base signal. Signal configuration module 2802 can receive the one or more signal processing specifications from a computer file. The file may contain one or more signal processing specifications previously specified by a user. Signal configuration module 2802 can also receive a signal processing specification via a graphical user interface (GUI) in which a user manually enters the signal processing specification using a series of computer mouse, touch, keyboard, and/or voice recognition data entry techniques, as would be appreciated by a person of ordinary skill in the art.

In response to receiving one or more signal processing specifications, signal configuration module 2802 can forward the one or more signal processing specifications to signal factory module 2804. Signal factory module 2804 can generate a signal module 2614 based on a signal processing specification. For example, signal factory module 2804 can generate a signal module 2614 as shown in FIG. 29.

FIG. 29 is a block diagram of a signal module 2614 generated by signal factory module 2804, according to some embodiments. Signal module 2614 can generate a processed signal from a base signal. Signal module 2614 includes an input packet queue 2902, a digital signal processor (DSP) 2904, and an output packet queue 2906. FIG. 29 can be discussed with reference to FIGS. 26 and 28.

Signal module 2614 includes input packet queue 2902, DSP 2904, and output packet queue 2906. Signal factory module 2804 can generate input packet queue 2902, DSP 2904, and output packet queue 2906 based on a signal processing specification from signal configuration module 2802. Input packet queue 2902 can store one or more packets from packet dispatcher 2610 for processing by DSP 2904. Input packet queue 2902 can be a queue data structure that stores items in the order that they are inserted. For example, the first item inserted into input packet queue 2902 is the first item removed from input packet queue 2902. In other words, input packet queue 2902 can be a first-in-first-out (FIFO) data structure. As would be appreciated by a person of ordinary skill in the art, input packet queue 2902 can be implemented using a linked list, an array, or various other data structure.

Output packet queue 2906 can store one or more packets processed by DSP 2904. Output packet queue 2906 can be a queue data structure that stores items in the order that they are inserted. For example, the first item inserted into output packet queue 2906 is the first item removed from output packet queue 2906. In other words, output packet queue 2906 can be a first-in-first-out (FIFO) data structure. As would be appreciated by a person of ordinary skill in the art, output packet queue 2906 can be implemented using a linked list, an array, or various other data structure.

Signal factory module 2804 can generate DSP 2904 based on a signal processing specification from signal configuration module 2802. Specifically, signal factory module 2804 can request DSP factory module 2808 to generate DSP 2904. DSP factory module 2808 can generate DSP 2904 based on a digital signal processing function specified in the signal processing specification. DSP factory module 2808 can further generate DSP 2904 based on one or more signal processing parameters associated with a digital processing function. For example, DSP factory module 2808 can generate DSP 2904 based on a low-pass filter function and a cutoff frequency specified in a signal processing specification.

A DSP 2904 is a software module capable of being executed by a processor (or processors) such as processor 8504 in FIG. 85. DSP 2904 can apply a digital processing function to one or more packets, and therefore one or more signal samples. As would be appreciated by a person of ordinary skill in the art, a digital processing function may be a mathematical algorithm that takes one or more signal samples as input, processes them, and produces one or more potentially modified signal samples as output. A digital processing function may be implemented using one or more mathematical operations such as a fast Fourier transform. As would be appreciated by a person of ordinary skill in the art, DSP 2904 can apply various types of digital processing functions. For example, DSP 2904 can apply a low-pass filter, a high-pass filter, a band-pass filter, a band-stop filter, a notch filter, a comb filter, an all-pass filter, or various other filters as would be appreciated by a person of ordinary skill in the art.

DSP 2904 can also apply a digital processing function that analyzes a signal for various characteristics. For example, DSP 2904 can apply a digital processing function that determines whether a noise anomaly or signal pattern is present in a signal. DSP 2904 can also analyze a signal by detecting repeated patterns in the signal. This may involve comparing the signal to a previously detected (or recorded or synthesized) signal pattern.

For example, DSP 2904 can determine a late potential in a signal. Specifically, DSP 2904 can determine a noise anomaly followed by subsequent noise anomalies occurring at the same time relative to a matched beat. Each subsequent noise anomaly at the same relative position can increase a confidence level that a late potential has been located. A display module 2618 can then display an indication of the late potential.

For example, such determination of a late potential by DSP 2904 can be used for a pulmonary vein potential filter. Specifically, a combination of a late post mid p-wave discrete electrogram with filtering for rapid conduction can be used to identify pulmonary vein potentials discrete from neighboring atrial and other structures. These signals can serve as the endpoint for ostia ablation to identify rapidly delay and exclusion. The system can be used for other thoracic veins, late ventricular electrograms above the semilunar valves, late potentials in diseased myocardium, and coronary sinus and vein of Marshal.

Similarly, DSP 2904 can determine an early activation in a signal. Specifically, DSP 2904 can determine an earliest sharp intracardiac signal above a selected threshold occurring within a predetermined segment before a reference point of a matched beat. A display module 2618 can then display an indication of the early activation.

DSP 2904 can detect a pattern in a signal using a correlation function. For example, DSP 2904 can detect a pattern using a mean absolute deviation algorithm. As would be appreciated by a person of ordinary skill in the art, DSP 2904 can use various other types of pattern matching algorithms.

DSP 2904 can detect a pattern based on various signal characteristics (also referred to as signal patterns). For example, DSP 2904 can detect a pattern based on shape, amplitude, and time characteristics. As would be appreciated by a person of ordinary skill in the art, DSP 2904 can detect a pattern based on various other types of signal characteristics.

DSP 2904 can also include one or more signal processing parameters. The signal processing parameters may control how DSP 2904 applies its digital processing function. For example, DSP 2904 can include one or more signal processing parameters that specify a threshold frequency or an amplitude for filtering. DSP 2904 can also include one or more signal processing parameters that specify a signal pattern to detect, or a noise threshold value.

DSP 2904 can apply its digital processing function to a packet in input packet queue 2902. In some embodiments, DSP 2904 can scan input packet queue 2902 for a new packet to process. In some other embodiments, DSP 2904 can get a notification that a new packet is available in input packet queue 2902. DSP 2904 can then retrieve the packet from input packet queue 2902.

DSP 2904 can apply its digital processing function to the retrieved packet. In other words, DSP 2904 can apply its digital processing function to the one or more signal samples in the packet. DSP 2904 can control how it applies its digital processing function to the one or more signal samples in the packet based on its one or more signal processing parameters. After processing the packet, DSP 2904 can store the packet in output packet queue 2906 for display by output module 2616.

As discussed below, each DSP 2904 can have an associated processing delay. The processing delay can represent the amount of time to complete processing of a packet by the digital processing function of DSP 2904. The processing delay can vary between different DSPs 2904. This variance in processing delay between different DSPs 2904 can cause the DSPs 2904 to output packets for display at different times, as discussed below.

After signal factory module 2804 completes generating input packet queue 2902, DSP 2904, output packet queue 2906, signal factory module 2804 can connect the output of input packet queue 2902 to the input of DSP 2904, and the output of DSP 2904 to the input of output packet queue 2906. Once signal factory module 2804 completes the connection, DSP 2904 can receive packets from input packet queue 2902 representing an unprocessed base signal. DSP 2904 can then process the packets using its digital processing function. DSP 2904 can output the processed packets to output packet queue 2906. Signal factory module 2804 can further configure input packet queue 2902 to receive packets from the base signal specified in the signal processing specification.

Once the signal module 2614 is created, signal factory module 2804 can add it to global signals table 2612. As discussed above, global signals table 2612 can be a fixed size array. Each element of the array can be associated with a given base signal. Moreover, each element of the array can be a fixed size array itself. Each element of this subarray can be associated with a given signal module 2614.

In some embodiments, signal factory module 2804 can add the created signal module 2614 to global signals table 2612 by adding a new array element to each subarray associated with a base signal. This new array element can correspond to the newly created signal module 2614. For example, if global signals table 2612 previously contained ten (10) signal modules 2614, the newly created signal module 2614 can be added at element number 11 in each subarray, for example.

Once the created signal module 2614 is added to global signals table 2612, a user (e.g., a physician) can assign the created signal module 2614 to a given base signal. In some embodiments, global signals table 2612 can indicate whether the created signal module 2614 is assigned to a given base signal by storing a ‘0’ or ‘1’ at the corresponding element in the subarray associated with the created signal module 2614. In some other embodiments, global signals table 2612 can indicate whether the created signal module 2614 is assigned to a given base signal by storing a reference to the created signal module 2614 at the corresponding element in the subarray.

Signal factory module 2804 can generate multiple signal modules 2614. Each signal module 2614 can have a DSP 2904 that applies a different digital signal processing function. As a result, each signal module 2614 can generate a different processed version of the same base signal. This can enable a user to analyze the same base signal in a variety of ways. A user may also want to analyze the time-aligned output of multiple versions of the same base signal. This can enable the user to compare different versions of the same signal at the same point in time or different points in time.

As noted above, conventional digital signal processing systems are often unable to synchronize the display of multiple processed signals in near real-time. This may be because different digital signal processing functions have different processing delays. For example, a current EP system may apply two different digital signal processing functions to the same base signal. But a medical team may want to synchronize the display of the two processed signals. For example, a medical team may want to compare an IC signal and an ECG signal at the same point in time in order to determine a clinical diagnosis. In other words, the medical team may want to time-align the display of the first processed signal with the display of the second processed signal in near real-time. But this may not be possible if the two different digital signal processing functions have different processing delays. This is because one of the digital signal processing functions may complete processing of the base signal more quickly than the other digital signal processing function. As a result, one processed signal may be displayed before the other processed signal.

The processing delay associated with a digital processing function may depend on the complexity of the function. For example, a digital processing function that performs low-pass filtering on a signal may be less computationally-intensive and use minimal memory. As a result, such a digital processing function may have a short processing delay. In contrast, another digital processing function may analyze a signal for particular signal characteristics. This type of digital processing function may be more computationally-intensive and use more memory, and therefore have a longer processing delay.

Because of the different processing delays, one processed signal may be displayed before another processed signal. This synchronization gap may become greater over time. For example, this synchronization gap may become greater where multiple signals are being processed and displayed in near real-time. This is because the difference in processing delay between two digital signal processing functions may be propagated to each new signal sample.

For example, a first digital signal processing function may have a processing delay of 10 milliseconds for a given base signal. A second digital signal processing function may have a processing delay of 20 milliseconds for the same base signal. The first digital signal processing function may complete processing of a first signal sample of the base signal at 10 milliseconds, and the second digital signal processing function may complete processing of the same first signal sample at 20 milliseconds. Thus, the first signal sample processed by the first digital signal processing function may be displayed at 10 milliseconds, and the first signal sample processed by the second digital signal processing function may be displayed at 20 milliseconds. In other words, the first signal sample processed by the first digital signal processing function may be displayed 10 milliseconds before the first signal sample processed by the second digital signal processing function.

This synchronization gap may increase when the second signal sample is processed. For example, the second signal sample may be received for processing by the first digital signal processing function at time 10 milliseconds, and the second signal sample may be received for processing by the second digital signal processing function at time 20 milliseconds. As a result, the second signal sample processed by the first digital signal processing function may be displayed at 20 milliseconds, and the second signal sample processed by the second digital signal processing function may be displayed at 40 milliseconds. In other words, the synchronization gap may increase by 10 milliseconds for the second signal sample; initially the synchronization gap is 10 milliseconds and subsequently the synchronization gap is 20 milliseconds.

This synchronization gap may increase where the digital signal processing is performed on a non-real-time operating system. Unlike a non-real-time operating system, a real-time operating system is a time bound system with well-defined fixed time constraints. A real-time operating system can guarantee that an application task is accepted and completed in a certain amount of time. In other words, a real-time operating system may provide a level of consistency concerning the amount of time it takes to complete a task.

In contrast, a non-real-time operating system cannot provide any guarantee that an application task is completed in a certain amount of time. For example, a non-real-time operating system may not provide a guarantee that the execution of a particular digital signal processing function is completed in a certain amount of time. As a result, there may be a high degree of variability concerning the amount of time it takes to complete a task. This may be problematic when attempting to synchronize the processing and display of multiple processed signals. This is because a processing delay associated with a digital processing function may vary with each execution. For example, a digital signal processing function may normally complete execution in 10 milliseconds. But on a non-real-time operating system, there may be no guarantee that the digital signal processing function completes execution after 10 milliseconds. For example, the digital signal processing function may complete execution in 30 milliseconds. This variability in processing delay may further increase the synchronization gap.

In some embodiments, this display synchronization problem is solved in a multipronged way using an input packet queue 2902 and an output packet queue 2906 of a signal module 2614, storing signal samples in a packet along with an associated tag, and equalizing the processing delays among one or more DSPs 2904.

An input packet queue 2902 and an output packet queue 2906 can solve the display synchronization problem in three ways. First, they ensure packets, and therefore signal samples, are processed and displayed sequentially. Second, an output packet queue 2906 can synchronize the display of packets at the same point in time by blocking the processing of more packets until existing packets are consumed by output module 2616. In other words, an output packet queue 2906 can provide a feedback mechanism to a DSP 2904 that indicates when the DSP 2904 can stop processing more packets. Finally, an input packet queue 2902 ensures a DSP 2904 has packets to process. For example, when an input packet queue 2902 is empty, a DSP 2904 can stop processing more packets. In other words, an input packet queue 2902 can provide a feedback mechanism to a DSP 2904 to indicate that there are no more packets to process.

DSP delay equalizer 2806 can also solve the display synchronization problem by equalizing processing delays across one or more DSPs 2904. As discussed above, different digital signal processing functions have different processing delays, which may cause the processed signals to be displayed out of sync. Therefore, if configuration path module 2620 generates multiple signal modules 2614, each with a DSP 2904 having a different digital signal processing function, each signal module 2614 can complete processing of a packet with a different processing delay. Because of these different processing delays, the processed signals may be displayed out of sync by output module 2616. DSP delay equalizer 2806 can solve this problem by equalizing the processing delays across the generated signal modules 2614.

In some embodiments, after configuration path module 2620 generates the one or more signal modules 2614, signal factory module 2804 can use DSP delay equalizer 2806 to equalize the processing delays of each generated signal module 2614 such that each signal module 2614 outputs a processed packet to its output packet queue 2906 at the same time. For example, DSP delay equalizer 2806 can determine the relative processing delay between two signal modules 2614. DSP delay equalizer 2806 can then use the determined relative delay to configure a DSP 2904 in the first signal module 2614 to complete processing of a packet at approximately the same time as a DSP 2904 in the second signal module 2614 is designed to complete processing of a packet.

In some embodiments, DSP delay equalizer 2806 can perform the equalization by scanning each generated signal module 2614. During the scan, DSP delay equalizer 2806 can request the processing delay associated with a DSP 2904 in each signal module 2614. DSP delay equalizer 2806 can request the processing delay using an application programming interface (API) of each signal module 2614. In response, each signal module 2614 can return its associated processing delay.

A signal module 2614 can store the processing delay associated with its DSP 2904. The processing delay may be a predefined value specified in the signal processing specification used to generate DSP 2904. In some other embodiments, DSP factory module 2808 can calculate the processing delay of a DSP 2904 based on various factors including the digital processing function used by the DSP 2904, the chosen signal processing parameters, and hardware characteristics such as the speed of the processor such as processor 5004, the size of the memory, and I/O latency.

After determining the processing delay associated with a DSP 2904 in each signal module 2614, DSP delay equalizer 2806 can determine the maximum processing delay among the signal modules 2614. For example, DSP delay equalizer 2806 can determine that signal module 2614-1 has a processing delay of 10 milliseconds, that signal module 2614-2 has a processing delay of 20 milliseconds, and that signal module 2614-N has a processing delay of 50 milliseconds. Based on this, DSP delay equalizer 2806 can determine that the maximum processing delay among the signal modules 2614 is 50 milliseconds.

After determining the maximum processing delay, DSP delay equalizer 2806 can configure the DSP 2904 of each signal module 2614 to have the maximum processing delay. For example, DSP delay equalizer 2806 can set the processing delay of the DSP 2904 of each signal module 2614 using an API. In response, each DSP 2904 can be designed to process a packet using its digital processing function and output the processed packet to its associated output packet queue 2906 at the end of the maximum processing delay. For example, in some embodiments, DSP 2904 can block its output to its output packet queue 2906 if it completes processing a packet prior to the end of the maximum processing delay. In some other embodiments, DSP 2904 can insert idle compute cycles during processing of a packet. As would be appreciated by a person of ordinary skill in the art, various other approaches may be used to cause DSP 2904 to output a processed packet to its output packet queue 2906 at the end of the maximum processing delay.

Packetization and the assignment of tags to packets can solve the display synchronization problem. As discussed above, each generated packet may include a fixed number of signal samples. Each packet may also include a tag indicating the packet's relative position among a sequence of packets. In order to synchronize the display of multiple signals, a display module 2618 can display packets having the same tag. In other words, the display module 2618 can synchronize its display using a tag.

As shown in FIG. 26, output module 2616 can include one or more display modules 2618-1 through 2618-N and review module 2624. Review module 2624 can be a software module capable of being executed by a processor (or processors) such as processor 5004. Review module 2624 can display one or more signals processed by one or more signal modules 2614 at a previous point in time. The display modules 2618 can each be software modules capable of being executed by a processor (or processors) such as processor 5004. A display module 2618 can display one or more live signals processed by one or more signal modules 2614. Each display module 2618 can operate independently of the other display modules 2618. In other words, each display module 2618 can simultaneously display one or more signals on one or more display devices such as an input/output device 8503 in FIG. 85. In some embodiments, each display module 2618 can display its associated one or more signals in a particular GUI window on a given display device.

Each display module 2618 can display one or more signals. Each display module 2618 can receive a packet from an associated output packet queue 2906 in a signal module 2614 in global signals table 2612. Display module 2618 can display a signal based on the packet.

FIG. 30 is a block diagram of a display module 2618, according to some embodiments. Display module 2618 includes a local signal table 3002, a packet index 3004, and display settings 3006. FIG. 30 is discussed with reference to FIG. 29.

As discussed, a display module 2618 can receive a packet from an associated output packet queue 2906 in a signal module 2614. To receive the packet, display module 2618 can maintain a reference to the associated output packet queue 2906 in the signal module 2614. When a display module 2618 is designed to display multiple signals, the display module 2618 can maintain references to the output packet queues 2906 associated with each signal being displayed. The display module 2618 can store the references in its local signal table 3002. Local signal table 3002 can contain a list of one or more references to the output packet queues 2906 associated with each signal being displayed. The display module 2618 can remove a reference from its local signal table 3002 when the associated signal module 2614 is no longer active.

In some embodiments, a display module 2618 can continuously scan its one or more associated output packet queues 2906 for new packets. Where the display module 2618 is associated with a single output packet queue 2906, each time the display module 2618 detects a new packet, it may display the packet on a display device. However, where the display module 2618 is associated with multiple output packet queues 2906, the display module 2618 may not immediately display a new packet detected in a particular output packet queue 2906. This is because display module 2618 can be designed to synchronize the display of multiple signals.

In some embodiments, where a given display module 2618 is designed to synchronize the display of multiple signals, the display module 2618 can detect a new packet in a particular output packet queue 2906. The display module 2618 can then determine the tag associated with the new packet. The display module 2618 can use this determined tag to synchronize the display of new packets from the other output packet queues 2906. For example, display module 2618 can wait to display any packets to the display device until after detecting new packets at the other output packet queues 2906 that have the same determined tag. Once display module 2618 detects new packets having the same tag at its other associated output packet queues 2906, the display module 2618 can simultaneously display the packets from its associated output packet queues 2906. The display module 2618 can display the multiple signals in a non-overlapping stackable format. Because the display module 2618 can display packets having the same tag, the resulting displayed signals may be time-aligned.

As previously stated, the type of preprocessing that packetizer 2606 can perform on any one of multiple signals can depend on the type of signal. In some embodiments, choice of preprocessing of a signal by packetizer 2606 can be automated. This allows for automated deployment of appropriate multiple filters, based on neighboring signals and ratio of far-field to near-field signals with minimal filtering, for example, to minimize noise and to target the signals of interest. As would be understood by a person of ordinary skill in the art, this type of automation can be effective in minimizing procedural time for low and medium volume operators, for example. Display module 2618 can similarly synchronize and display the multiple signals as new packets are detected from the automated process.

Display module 2618 can maintain the current active tag to display in packet index 3004. Upon detecting a new packet in a particular output packet queue 2906, the display module 2618 can determine the tag of the new packet. Display module 2618 can then set packet index 3004 to the determined tag.

In some embodiments, a high-frequency rapid conducting signals filter can be applied to multiple electrodes, such as with a basket or balloon-based catheter, to identify conduction tissue, such as, for example, distal Purkinje and annular rapid conducting tissue. Such annular tissue can be quickly targeted for ablation due to the prominence of its signal. Based on dynamic tagging of packets from packetizer 2606, the display module 2618 can continue to visualize the signal as a point of reference to guide ablation catheter movement and can be used to terminate local energy delivery when a pathogenic signal of interest has decayed while ablating. As illustrated by this example, the preprocessing and continued processing of the system can allow a physician to continue to see signals even when ablating.

A display module 2618 can include display settings 3006. Display settings 3006 can include one or more parameters that control how display module 2618 displays its one or more associated signals. Display settings 3006 can specify colors to display the one or more associated signals. Display settings 3006 can specify a view format such as a waterfall view, dynamic view, or triggered view as discussed below. Display settings 3006 can specify a sweep speed for the one or more signals. Display settings 3006 can contain various other types of display settings as would be appreciated by a person of ordinary skill in the art. Display settings 3006 can be designed by a user as discussed below.

Review module 2624 can display one or more signals processed by one or more signal modules 2614 at a previous point in time. This can enable a user (e.g., a physician) to analyze the one or more signals long after they have been generated and displayed. In some embodiments, review module 2624 can capture a display of one or more signals in a display module 2618 in response to a command. For example, a user can click a button in a GUI to capture the current display of a display module 2618. The captured display can include the previously displayed visualization of the one or more signals at the time of capture. In some embodiments, the display module 2618 can pause its display of new packets in response to the capture of its current display.

In some embodiments, review module 2624 can capture the display of the one or more signals in the display module 2618 by determining a capture configuration of the display module 2618. The capture configuration can include the one or more active signals modules 2614 for the display module 2618, the capture time, the selected view for the display module 2618, the color scheme for the one or more displayed signals, and various other settings as would be appreciated by a person of ordinary skill in the art. After determining the capture configuration, review module 2624 can apply the capture configuration to previously stored signal samples.

As discussed above, input module 2604 can store one or more signal samples for each base signal in a storage for later analysis by review module 2624. Review module 2624 can capture a display of the one or more signals in the display module 2618 by applying the determined capture configuration to these stored signal samples. Specifically, review module 2624 can select the stored signal samples at the capture time in the capture configuration. Review module 2624 can then process the selected signal samples using the active signal modules 2614 in the capture configuration. Review module 2624 can also display the selected signal samples using the selected view, the color scheme, and various other settings in the capture configuration. Thus, review module 2624 can enable a user to review one or more processed signals for a display module 2618 at a particular point in time, and subject to a particular configuration.

In some embodiments, review module 2624 can enable a user to change the reviewed interval for a display module 2618. For example, the user can “rewind” to a different point in time in the past (e.g., 5 minutes ago). After the capture time is changed, review module 2624 can display the one or more processed signals for the display module 2618 at the new review time index.

FIG. 31 is a block diagram of monitoring module 2622, according to some embodiments. Monitoring module 2622 includes queue monitor 3102 and report module 3104. Queue monitor 3102 and report module 3104 can be software modules capable of being executed by a processor (or processors) such as processor 5004.

Monitoring module 2622 can be continuously executed while signal path module 2602 is being executed. For example, monitoring module 2622 can be executed as a separate thread of execution by a processor. Monitoring module 2622 can determine whether there are issues in the execution of signal path module 2602.

In some embodiments, queue monitor 3102 can periodically scan queues in the signal path module 2602. For example, queue monitor 3102 can scan the queues 2702 in queuing module 2608. Queue monitor 3102 can also scan the input packet queues 2902 and the output packet queues 2906 in the one or more signal modules 2614. Queue monitor 3102 can determine the status of each queue during the scan. For example, queue monitor 3102 can determine the length of each queue during the scan. In some embodiments, if queue monitor 3102 determines a queue has an error status, queue monitor 3102 can request report module 3104 to display the error status on a display device. For example, queue monitor 3102 can determine that a queue's length is continuously increasing. In response, queue monitor 3102 can request report module 3104 to display an error that indicates that the particular queue has an incorrect length.

FIG. 32 illustrates an example adjustment of a sweep speed for a display module 2618, according to some embodiments. FIG. 32 includes a live viewing area 3202 and a sweep speed 3204. FIG. 32 is discussed with reference to FIG. 26.

Live viewing area 3202 can contain the near real-time display of a display module 2618. In FIG. 32, live viewing area 3202 includes the near real-time display of fourteen (14) different signals (e.g., processed or base signals).

Sweep speed 3204 can be a GUI widget that allows a user to select a sweep speed for live viewing area 3202. A sweep speed may represent a time scale of one or more signals displayed in live viewing area 3202. For example, the sweep speed may range from 10 mm per second to 1000 mm per second. In FIG. 32, sweep speed 3204 is shown being selected to be 50 mm per second. As would be appreciated by a person of ordinary skill in the art, the choice of sweep speed may influence the level of displayed detail, and therefore may be set based on the size of the display screen.

FIG. 33 illustrates signal management for a display module 2618, according to some embodiments. FIG. 33 includes a signal management window 3302. FIG. 33 is discussed with reference to FIG. 26.

Signal management window 3302 can include available signals 3304 and signal settings 3306. Available signals 3304 can contain one or more signals that can be selected for display by a display module 2618. For example, in FIG. 33, available signals 3304 contain fourteen (14) signals that can be selected for display by a display module 2618. Available signals 3304 can display various information about each signal. For example, available signals 3304 can display the name of the signal and whether the signal is processed by a particular signal module 2614.

Signal settings 3306 can display various settings that can be set for each signal. For example, in FIG. 33, signal settings 3306 enables a user to change the name of each signal or assign each signal a particular color. These settings may be stored in display settings 3006 in display module 2618. Signal settings 3306 can also enable a user to change various processing parameters associated with each signal. These processing parameters may be stored in the one or more signal processing parameters of a DSP 2904 of a signal module 2614 associated with the given signal.

FIG. 34 illustrates an example adjustment of zoom and clip factors for a display module 2618, according to some embodiments. FIG. 34 includes a live viewing area 3402 and a display settings window 3404. FIG. 34 is discussed with reference to FIG. 26.

Live viewing area 3402 can contain the near real-time display of a display module 2618. In FIG. 34, live viewing area 3402 includes the near real-time display of fourteen (14) different signals (e.g., processed or base signals).

Display settings window 3404 can include a zoom factor 3406 and a clip factor 3408. Zoom factor 3406 can be a GUI widget to select a zoom factor for a particular signal in live viewing area 3402. The selected zoom factor can increase or decrease the size of the particular signal. For example, zoom factor 3406 can increase the size of a particular signal from 0.02 to times 40.

Clip factor 3408 can be a GUI widget permitting a user to select a clip factor for a particular signal in live viewing area 3402. The selected clip factor can control how much a signal overshoots across the display screen. For example, a user can adjust the clip factor to reduce the actual area of where the particular signal is displayed so that if the particular signal is large, it does not extend beyond the whole display screen so as to be partially unviewable.

FIG. 35 illustrates pattern search management for a display module 2618, according to some embodiments. FIG. 35 includes a live viewing area 3502 and a pattern search window 3504. FIG. 35 is discussed with reference to FIG. 26.

Live viewing area 3502 can contain the near real-time display of a display module 2618. Pattern search window 3504 can be a GUI window that enables a user to load or specify a signal pattern to search. For example, in FIG. 35, a user may create or load a search for a late potential or early activation in one or more signals. The user may also specify various parameters for the search such as a search interval, heat detection confidence percentage, detection confidence percentage, or other parameters as would be appreciated by a person of ordinary skill in the art. The signal pattern to search for may be stored in the one or more signal processing parameters of a DSP 2904 of a signal module 2614 associated with the given signal.

FIG. 36 illustrates a late potential search result highlighted in a display of a display module 2618, according to some embodiments. FIG. 36 includes a live viewing area 3602. FIG. 36 is discussed with reference to FIG. 26.

Live viewing area 3602 can contain the near real-time display of a display module 2618 subject to a late potential search. A user may create or load the search for the late potential as previously illustrated in FIG. 35. Once a search is initiated, live viewing area 3602 can display late potentials found in one or more signals. Live viewing area 3602 can display the found late potentials with a detection confidence percentage. For example, in FIG. 36, found late potential 3604 is shown with an 83% detection confidence. Live viewing area 3602 can also display a tally of the total late potentials found.

FIG. 37A illustrates using a display module 3618 configured as waterfall view, according to some embodiments. FIG. 37A includes a live viewing area 3702. FIG. 37A is discussed with reference to FIG. 26.

Live viewing area 3702 can contain the near real-time display of a display module 2618. Live viewing area 3702 can use a waterfall view to display the near real-time display of a display module 2618. In waterfall view, signals can be displayed side by side and vertically stacked on top of each other as a pattern is matched. Specifically, a user can select a pattern to match in a first signal (e.g., a specific beat pattern). When the pattern is detected in the first signal, display module 2618 can display a portion of the first signal that matches the pattern next to the corresponding portion of a second signal (e.g., an IC signal). The user can select the size of the portion of the first signal and the size of the portion of the second signal to be displayed. For example, the user can select the size of the portion of the first signal using a time interval (e.g., 150 milliseconds).

In waterfall view, each time the pattern is detected in the first signal, display module 2618 can vertically display each new portion of the first signal that matches the pattern along with the corresponding portion of the second signal. In other words, in waterfall view, display module 2618 can display signals along a vertical time axis.

In FIG. 37A, live viewing area 3702 illustrates the near real-time display of two different signals (e.g., V2[P1] and AB1.d) in a waterfall view. In FIG. 37A, signals V2[P1] and AB1.d are displayed side by side stacked on top of each other. For example, at around time 10 seconds, signal portion 3704 is displayed side by side with signal portion 3706. Signal portion 3704 can represent a portion of signal V2[P1] that matches a given pattern (e.g., beat P1, lead V2) at around time 10 seconds. Signal portion 3706 can represent the corresponding portion of signal AB1.d at the time the given pattern matched signal V2[P1].

A user (e.g., a physician) can find waterfall view advantageous. First, waterfall view enables a user to compare corresponding portions of two signals side by side. Second, waterfall view can display signals on a display screen longer because the signals are vertically stacked. In contrast, when signals are displayed left to right, it is often difficult for a user to analyze the signals because they are no longer displayed on the display screen after a short period of time.

FIG. 37B illustrates the correspondence between signals in a regular display module 2618 and a display module 2618 configured as waterfall view, according to some embodiments. FIG. 37B includes a live viewing area 3708 and a waterfall view 3710. FIG. 37B is discussed with reference to FIG. 26.

In FIG. 37B, live viewing area 3708 illustrates the near real-time display of two different signals (e.g., V2[P1] and AB1.d). Waterfall view 3710 illustrates the near real-time display of the same two signals, except signals V2[P1] and AB1.d are displayed side by side so as to appear stacked on top of each other. In waterfall view 3710, each time a signal pattern in a signal is detected, display module 2618 can vertically display the portion of the signal that matches the signal pattern along with the corresponding portion of a second signal.

For example, in FIG. 37B, signal portion 3712 of signal V2[P1] contains a signal pattern. Corresponding signal portion 3714 of signal AB1.d corresponds to signal portion 3712 at the time of detection. In FIG. 37B, waterfall view 3710 displays signal portion 3712 and corresponding signal portion 3714 side by side (e.g., together) each time the signal pattern is detected in signal V2[P1]. In FIG. 37B, waterfall view 3710 displays a portion of signal V2[P1] that matches the signal pattern along with a corresponding portion of signal AB1.d from oldest to newest. In other words, in FIG. 37B, waterfall view 3710 displays heats that scroll up in time with the oldest beats at the top and the newest beats at the bottom. As would be appreciated by a person of ordinary skill in the art, waterfall view 3710 can display the beats in various other ways such as newest beats at the top and oldest beats at the bottom.

FIG. 37C illustrates using a display module 2618 configured as dynamic view, according to some embodiments. FIG. 37C includes a live viewing area 3716. FIG. 37C is discussed with reference to FIG. 26.

Live viewing area 3716 can contain the near real-time display of a display module 2618. Live viewing area 3716 can use a dynamic view to display the near real-time display of a display module 2618. In dynamic view, a user can select a trigger for a signal (e.g., a correlation with a stored beat). The user can select the trigger from a plurality of trigger types. A trigger type can be a signal characteristic of interest that is associated with a secondary event of interest. When the trigger occurs, display module 2618 can dynamically adjust the offset of the signal so that it is pinned to a baseline. This can prevent the signal from progressing off the display screen. This is often important in clinical settings where the height of a signal peak can indicate a particular type of injury, and a signal plateau can indicate the effectiveness of an ablation lesion, for example.

In FIG. 37C, live viewing area 3716 illustrates a reference beat measured on a unipolar signal (e.g., Uni1) at a reference time (e.g., reference time 3724). For example, this can occur during ablation. In FIG. 37C, signal 3718 can be the initial beat, signal 3720 can be the current beat, and signal 3722 can be the maximum recorded beat since signal Uni1 was captured at reference time 3724. As discussed, in dynamic view, a user can specify a reference location that determines a point in a signal that is pinned to a baseline. In FIG. 37C, this point is at pinned location 3726 (e.g., 0.0 mV) on the screen for signal Uni1. This can cause signal Uni1 to be offset so that it is pinned at pinned location 3726.

FIG. 37D illustrates using a display module 2618 configured as trigger view, according to some embodiments. FIG. 37D includes a live viewing area 3728 and a trigger view 3730. FIG. 37D is discussed with reference to FIG. 26.

Live viewing area 3728 can contain the near real-time display of a display module 2618. In FIG. 37D, trigger view 3730 illustrates the display of live viewing area 3728 using a trigger view. In trigger view 3730, a user can select a first signal (e.g., pacing signal 3732) that triggers the display of other signals (e.g., II signal 3734, Uni Dist signal 3736, and Uni Prox signal 3738). The user can select a particular trigger for the first signal. The user can select the trigger from a plurality of trigger types. A trigger type can be a signal characteristic of interest that is associated with a secondary event of interest. For example, the user can select a particular voltage (e.g., 60 millivolts) for the first signal. A person of ordinary skill in the art would understand that other signal characteristics can be selected. When the trigger occurs, display module 2618 can display the specified one or more signals synchronized in time and stacked vertically in the display. A user (e.g., physician) can find trigger view advantageous. This is because it can enable the user to more easily view events that happen relative to an event (e.g., start of pacing signal 3732).

In trigger view 3730, a user can also specify a time after the trigger occurs where data is pinned to the baseline. For example, in FIG. 37D, the user sets the time to approximately 70 ms after the trigger occurs. In FIG. 37D, in response to user setting the time to approximately 70 ms after the trigger occurs, Uni Dist signal 3736 and Uni Prox signal 3738 are pinned and always in view in trigger view 3730. In contrast, in FIG. 37D, Uni Dist signal 3736 and Uni Prox signal 3738 are not in view in live viewing area 3728 because they are not pinned to a baseline.

FIG. 38 illustrates the capture of signals in a display of a display module 2618 configured as a review window, according to some embodiments. FIG. 38 includes a live viewing area 3802 and a review window 3804. FIG. 38 is discussed with reference to FIG. 26.

Live viewing area 3802 can contain the near real-time display of a display module 2618. Review window 3804 can contain a previous display shown in live viewing area 3802. To capture the display of live viewing area 3802, a user may submit a capture request. For example, in FIG. 38, a user may click Review Button 3806. In response, review module 2624 can determine a capture configuration of the display module 2618. The capture configuration can include the one or more active signals modules 2614 for the display module 2618, a capture time, a selected view for the display module 2618, a color scheme for the one or more displayed signals, and various other settings as would be appreciated by a person of ordinary skill in the art. After determining the capture configuration, review module 2624 can apply the capture configuration to previously stored signal samples and display the output in review window 3802.

FIG. 39 illustrates amplitude measurement performed in a display of a display module 2618 configured as a review window, according to some embodiments. FIG. 39 includes a live viewing area 3902 and a review window 3904. FIG. 39 is discussed with reference to FIG. 26.

Live viewing area 3902 can contain the near real-time display of a display module 2618. Review window 3904 can contain a previously-captured display shown in live viewing area 3802. A user may analyze the previously-captured output in review window 3904 using vertical and horizontal calipers. Horizontal calipers can be a GUI selection widget. A user can use horizontal calipers to measure amplitude in millivolts (mV) for a particular signal. For example, as shown in FIG. 39, a user can click at the top and bottom of the V1 signal to generate two horizontal lines (e.g., caliper lines 3908 and 3910). The user may then hover the cursor along the V1 signal to display the measured amplitude at a particular point in time (e.g., measurement 3906). Similarly, vertical calipers can also be a GUI selection widget. A user can use vertical calipers to measure time in milliseconds, or beats per minute (BPM). A user can click at a left point and right point along a signal to generate two vertical lines and display the measured time, or beats per minute, between the two vertical lines, as illustrated in FIG. 65. For example, the time between vertical calipers 6502 and 6504 is 464 msec or 129 BPM, as displayed in the pop-up box 6506.

The following method descriptions for processing and displaying multiple signals in near-real time are provided for embodiments related to ECG and IC signal visualization. A person of ordinary skill in the art would understand that these methods can apply equally to visualization of other small physiologic signals.

FIG. 40 is a flowchart for a method 4000 for processing and displaying multiple signals in near real-time, according to some embodiments.

Method 4000 shall be described with reference to FIG. 26. However, method 4000 is not limited to that example embodiment.

In 4002, configuration path module 2620 configures one or more signal modules 2614. 4002 can be performed by method 4100 in FIG. 41.

In 4004, input module 2604 receives one or more signal samples for one or more signals. For example, input module 2604 can receive one or more signal samples for an IC signal, and one or more signal samples for an ECG signal 4004 can be performed by method 4400 in FIG. 44.

In 4006, input module 2604 dispatches the one or more signal samples to packetizer 2606.

In 4008, packetizer 2606 converts the one or more signal samples to one or more packets. 4008 can be performed by method 4500 in FIG. 45.

In 4010, packetizer 2606 dispatches the one or more packets to queuing module 2608. 4010 can be performed by method 4600 in FIG. 46.

In 4012, packet dispatcher 2610 dispatches a packet from queuing module 2608 to a signal module 2614 associated with the packet 4012 can be performed by method 4700 in FIG. 47.

In 4014, the signal module 2614 of 4012 processes the packet using a DSP 2904, 4014 can be performed by method 4800 in FIG. 48.

In 4016, a display module 2618 associated with the signal module 2614 of 4012 displays the processed packet to a display screen 4016 can be performed by method 4900 in FIG. 49.

FIG. 41 is a flowchart for a method 4100 for configuring one or more signal modules 2614, according to some embodiments.

Method 4100 shall be described with reference to FIG. 26. However, method 4100 is not limited to that example embodiment.

In 4102, signal configuration module 2802 can receive one or more signal processing specifications. A signal processing specification may specify a base signal to process, the lengths of input and output packet queues for a signal module 2614, a digital signal processing function to process the base signal, and one or more associated parameters for the digital signal processing function. In some embodiments, signal configuration module 2802 can receive a signal processing specification from a file stored in memory. In some other embodiments, signal configuration module 2802 can receive a signal processing specification from a GUI that enables a user to manually enter the signal processing specification.

In 4104, signal configuration module 2802 dispatches the one or more signal processing specifications to signal factory module 2804.

In 4106, signal factory module 2804 generates a signal module 2614 for each signal processing specification. 4106 can be performed by method 4200 in FIG. 42.

FIG. 42 is a flowchart for a method 4200 for generating a signal module 2614 from a signal processing specification, according to some embodiments.

Method 4200 shall be described with reference to FIG. 26. However, method 4200 is not limited to that example embodiment.

In 4202, signal factory module 2804 generates an input packet queue 2902 of the signal module 2614 based on the signal processing specification in 4106 of FIG. 41. For example, signal factory module 2804 generates an input packet queue 2902 by creating a queue data structure of the length specified in the signal processing specification.

In 4204, signal factory module 2804 generates an output packet queue 2906 of the signal module 2614 based on the signal processing specification. For example, signal factory module 2804 generates an output packet queue 2806 by creating a queue data structure of the length specified in the signal processing specification.

In 4206, signal factory module 2804 generates a DSP 2904 of the signal module 2614 using DSP factory module 2808 based on the signal processing specification. Specifically, signal factory module 2804 can request DSP factory module 2808 to generate the DSP 2904 based on the digital processing function and one or more signal processing parameters specified in the signal processing specification. For example, DSP factory module 2808 can generate DSP 2904 based on a low-pass filter function and a specific cutoff frequency specified in the signal processing specification.

In 4207, signal factory module 2804 connects the generated input packet queue 2902, the generated DSP 2904, and the generated output packet queue 2906 of the signal module 2614. Specifically, signal factory module 2804 connects the output of the input packet queue 2902 to the input of DSP 2904. Signal factory module 2804 further connects the output of DSP 2904 to the input of output packet queue 2906.

In 4210, signal factory module 2804 configures input packet queue 2902 to receive packets dispatched from packet dispatcher 2610. In some embodiments, signal factory module 2804 can add a rule to a lookup table associated with packet dispatcher 2610. The rule may specify that packets associated with a given signal can be processed by a given signal module 2614.

In 4212, signal factory module 2804 uses DSP delay equalizer 2806 to equalize the associated processing delays of each generated signal module 2614 such that each signal module 2614 outputs a processed packet to its output packet queue 2906 at the same time. 4210 can be performed by method 4300 in FIG. 43,

FIG. 43 is a flowchart for a method 4300 for equalizing the processing delay associated with each DSP 2904 of the one or more signal modules 2614, according to some embodiments.

Method 4300 shall be described with reference to FIG. 26. However, method 4300 is not limited to that example embodiment.

In 4302, DSP delay equalizer 2806 requests the processing delay associated with each DSP 2904 of the one or more signal modules 2614. DSP delay equalizer 2806 can request the processing delay of a DSP 2904 using an API of its associated signal module 2614.

In 4304, DSP delay equalizer 2806 receives the processing delay of a DSP 2904 from each of the one or more signal modules 2614.

In 4306, DSP delay equalizer 2806 determines a maximum processing delay among the one or more received processing delays.

In 4308, DSP delay equalizer 2806 sets a DSP 2904 of each of the one or more signal modules 2614 to the maximum processing delay. For example, DSP delay equalizer 2806 can set the processing delay of a DSP 2904 of each signal module 2614 using an API. In response, each DSP 2904 can be designed to process a packet using its digital processing function and output the processed packet to output packet queue 2906 at the end of the maximum processing delay. In some embodiments, a DSP 2904 can block its output to output packet queue 2906 if it completes processing a packet using its digital processing function prior to the end of the maximum processing delay.

FIG. 44 is a flowchart for a method 4400 for receiving one or more signal samples for one or more signals using input module 2604, according to some embodiments.

Method 4400 shall be described with reference to FIG. 26. However, method 4400 is not limited to that example embodiment.

In 4402, input module 2604 receives signal samples for a base signal from a hardware device (e.g., an electrode attached to a patient) or data stored in a computer file. For example, the computer file may contain a previously recorded session of signal samples received from a hardware device. As would be appreciated by a person of ordinary skill in the art, input module 2604 can simultaneously receive signal samples for multiple based signals.

In 4404, input module 2604 dispatches the received signal samples to packetizer 2606.

FIG. 45 is a flowchart for a method 4500 for converting one or more signal samples to one or more packets using packetizer 2606, according to some embodiments.

Method 4500 shall be described with reference to FIG. 26. However, method 4500 is not limited to that example embodiment.

In 4502, packetizer 2606 receives one or more signal samples from input module 2604.

In 4504, packetizer 2606 can optionally preprocess the one or more signal sa pies. For example, packetizer 2606 can convert the binary values of the one or more signal samples to their corresponding physical values. As would be appreciated by a person of ordinary skill in the art, packetizer 2606 can perform various other types of preprocessing.

In 4506, packetizer 2606 generates a packet containing the one or more signal samples for a given base signal. Packetizer 2606 can store a predefined number of signal samples in the packet. In some embodiments, packetizer 2606 can use timer 2605 to ensure that each packet contains the same number of signal samples.

Specifically, packetizer 2606 can store signal samples received from input module 2604 into the packet until timer 2605 is triggered.

In 4508, packetizer 2606 assigns a tag to the generated packet. The tag may correspond to a tune period in which the one or more signal samples in the packet were received. Packetizer 2606 can assign a new tag to each subsequent packet. For example, packetizer 2606 can first generate a packet containing sixteen (16) signal samples for a given base signal. In this case, packetizer 2606 can store the first set of signal samples in a packet with a tag of 0. Packetizer 2606 can store the second set of signal samples in a packet with a tag of 15. Packetizer 2606 can store the subsequent sets of signal samples in packets with tags of 31, 47, 64, etc.

FIG. 46 is a flowchart for a method 4600 for dispatching a packet containing one or more signal samples to queueing module 2608, according to some embodiments.

Method 4600 shall be described with reference to FIG. 26. However, method 4600 is not limited to that example embodiment.

In 4602, packetizer 2606 determines a base signal associated with a newly generated packet.

In 4604, packetizer 2606 determines a queue 2702 in queuing module 2608 associated with the determined base signal. Packetizer 2606 can determine that a queue 2702 is associated with the determined base signal using a lookup table.

In 4606, packetizer 2606 dispatches the packet containing the one or more signal samples to the determined queue 2702.

FIG. 47 is a flowchart for a method 4700 for dispatching a packet from queuing module 2608 to a signal module 2614 associated with the packet, according to some embodiments.

Method 4700 shall be described with reference to FIG. 26. However, method 4700 is not limited to that example embodiment.

In 4702, packet dispatcher 2610 continuously scans a queue 2702 in queueing module 2608.

In 4704, packet dispatcher 2610 detects a new packet in the queue 2702.

In 4706, packet dispatcher 2610 determines one or more signal modules 2614 in global signals table 2612 that are designed to process the new packet. Because the new packet can be dispatched to multiple signal modules 2614 (e.g., multiple copies or “instances” of the packet), the base signal associated with the packet can be simultaneously processed using different digital processing functions of the signal modules 2614.

In some embodiments, packet dispatcher 2610 can determine one or more signal modules 2614 that are designed to process an instance of the new packet using global signals table 2612. For example, global signals table 2612 can be a fixed size array. Each element of the array can be associated with a given base signal, and thus a given a queue 2702. Moreover, each element of the array can be a fixed size array itself. Each element of this subarray can be associated with a given signal module 2614. Thus, packet dispatcher 2610 can determine one or more signal modules 2614 that are designed to process the new packet by checking the corresponding element in the subarray associated with the base signal of the new packet.

In some other embodiments, packet dispatcher 2610 can determine the one or more signal modules 2614 that are designed to process the new packet using a lookup table. Specifically, the lookup table may map the queue 2702 to one or more signal modules 2614.

In 4706, packet dispatcher 2610 dispatches the new packet to the determined one or more signal modules 2614 in global signals tables 2612 for processing. Specifically, packet dispatcher 2610 inserts the new packet into the input packet queues 2902 of the determined one or more signal modules 2614.

FIG. 48 is a flowchart for a method 4800 for processing a packet using a signal module 2614 associated with the packet, according to some embodiments.

Method 4800 shall be described with reference to FIG. 26. However, method 4800 is not limited to that example embodiment.

In 4802, DSP 2904 detects whether a new packet is available in the input packet queue 2902 of the signal module 2614. In some embodiments, DSP 2904 can scan the input packet queue 2902 for a new packet to process. In some other embodiments, DSP 2904 can get a notification that a new packet is available in the input packet queue 2902.

In 4804, DSP 2904 retrieves the new packet from input packet queue 2902 of the signal module 2614.

In 4806, DSP 2904 processes the new packet using its associated digital signal processing function. Specifically, DSP 2904 can apply its digital processing function to the one or more signal samples in the packet. In some embodiments, DSP 2904 can control how it processes the packet using its digital processing function based on one or more signal processing parameters designed for DSP 2904.

In 4808, DSP 2904 outputs the processed packet to output packet queue 2906. In some embodiments, DSP 2904 can output the processed packet to output packet queue 2906 based on its designed maximum processing delay.

FIG. 49 is a flowchart for a method 4900 for displaying a processed packet to a display screen using display module 2618, according to some embodiments.

Method 4900 shall be described with reference to FIG. 26. However, method 4900 is not limited to that example embodiment.

In 4902, display module 2618 determines what one or more signal modules 2614 from which to display processed packets. In some embodiments, display modules 2618 can determine what one or more signal modules 2614 to display processed packets from by maintaining references to the output packet queues 2906 of the one or more signal modules 2614. Display module 2618 can store the references in local signal table 3002.

In 4904, display module 2618 detects that a new packet is available in an output packet queue 2906 of one of the determined signal modules 2614.

In 4906, display module 2618 receives the new packet from the output packet queues 2906 of the one of the determined signal modules 2614.

In 4908, display module 2618 determines a tag associated with new packet.

In 4910, display module 2618 receives new packets from the other output packet queues 2906 that match the determined tag.

In 4912, display module 2618 simultaneously displays the received new packets for one or more signal modules to a display screen. Because display module 2618 displays new packets having the same tag, display module 2618 synchronizes the display of the signals associated with the new packets.

Methods 4000, 4100, 4200, 4300, 4400, 4500, 4600, 4700, 4800, 4900 can be performed by processing logic that can comprise hardware (e.g., circuitry, dedicated logic, programmable logic, microcode, etc.), software (e.g., instructions executing on a processing device), or a combination thereof. It is to be appreciated that not all steps may be needed to perform the disclosure provided herein. Further, some of the steps may be performed simultaneously, or in a different order than shown in FIGS. 40-49, as will be understood by a person of ordinary skill in the art.

In some embodiments, DSP 2904 can be based on a notch filter. A electrophysiology lab with numerous pieces of equipment can tend to have substantial line frequencies and harmonics (e.g., noise) interfering with cardiac recordings. In North America this can be primarily 60 Hz plus harmonics. FIG. 50 illustrates an example of a signal (e.g., triangular spikes 5002) with superimposed 60 Hz noise 5004, according to some embodiments.

To get accurate cardiac recordings, it is often desirable to remove the noise while preserving the signal of interest. Conventional approaches to removing 60 Hz noise involve using a notch filter with a transmission zero at 60 Hz. FIG. 51 illustrates an example of a conventional approach to removing 60 Hz noise using a notch filter with a transmission zero (a single notch) 5102 at 60 Hz, according to some embodiments.

FIG. 52 illustrates an example of the result of applying the conventional filter of FIG. 51, according to some embodiments. As shown in FIG. 52, the 60 Hz signal is removed from the input signal 5202 to produce the filtered signal 5204. However, the conventional filter can suffer from multiple problems. For example, after a large spike 5206, the conventional filter can introduce overshoot and ringing (e.g., transient responses) 5208 into the signal. This overshoot and ringing can be an artifact of the filter and not part of the original input signal. This can result in a less accurate cardiac recording.

In addition, a conventional 60 Hz notch filter may not reduce any of the harmonics of 60 Hz. For example, as illustrated in FIG. 53, if interference in the input signal 5302 is evaluated with both 60Hz and 180 Hz, the 180 Hz harmonic can still be present at the output of the conventional filter. FIG. 53 illustrates an example of the 180 Hz harmonic still present in the filtered signal 5304 at the output of the conventional filter of FIG. 51, according to some embodiments.

Thus, as illustrated in FIG. 53, conventional notch filters can suffer from two problems. First, conventional notch filters can introduce overshoot and ringing 5306 into the signal. Second, conventional notch filters may not reduce any of the higher level harmonics.

In some embodiments. DSP 2904 can apply a notch filter that does not introduce overshoot and ringing into a signal and reduces higher level harmonics, not just the primary harmonic. The notch filter of DSP 2904 can solve the above technical problems of conventional notch filters by extracting the interfering noise and subtracting it from the noisy signal. This can remove the interference without creating the artifacts associated with conventional notch filters (e.g., overshoot and ringing). The notch filter of DSP 2904 can reproduce one cycle of the interfering signal in a separate buffer (also referred to as a cycle buffer, noise buffer, or data buffer) and subtract it from the noisy signal to extract the original data. Since the line frequency noise can be constant or nearly constant, the notch filter of DSP 2904 can use some variation of averaging to refine the estimate over time. Because the frequency can be known, the buffer size can be predetermined. In addition, a buffer that stores exactly one cycle can also store an integral number of higher frequency harmonics which can be subtracted from the noisy data. FIG. 54 illustrates an example of the notch filtering of DSP 2904 for a signal with 60 Hz and 180 Hz noise, according to some embodiments. Because the line frequency noise is constant, one cycle of interference 5402 can be reproduced and subtracted from each cycle 5404 of consecutive cycles in the input signal.

In the case of 60 Hz noise and a 2000 samples-per-second sample rate, 33⅓ samples can be stored in the buffer. Since there can be an integral number of samples in the buffer, the notch filter of DSP 2904 can choose to use 100 samples and store exactly 3 cycles of 60 Hz. FIG. 55 illustrates an example of the notch filter of DSP 2904 using 100 samples of the input signal 5502 and storing exactly 3 cycles of 60 Hz 5504, according to some embodiments.

To accumulate the steady state noise in the buffer, data can be gathered in the “quiet times” of the waveforms. As would be appreciated by a person of ordinary skill in the art, a quiet time can be a period of time in the input signal where there are no large spikes or edges. Quiet times can be determined by calculating the slope of the signal. FIG. 56 illustrates an example of the notch filter of DSP 2904 calculating quiet times in an input signal 5602, according to some embodiments. Three cycles of noise data (interference) 5604 can be gathered in a buffer during a quiet time 5606. Subsequent cycles 5608, 5610, 5612 are averaged to build up an accurate copy of the interference 5604. Because the cycle time is constant for cycles 5606, 5608, 5610, 5612, only cycles of the fundamental frequency and harmonic frequencies accumulate. Cycles of other frequencies average out to zero.

For each new point that is sampled from the incoming data, a determination can be made to decide if it is in the “quiet time” of the signal. A quiet time can be determined by calculating a slope of the signal. If the slope is above a threshold value, a quiet time can be determined to have begun. If the new point is in a quiet time, it can be averaged with the previously stored data at that location in the buffer. As time progresses, this averaging process can accumulate a replica of the noise which can be subtracted from the noisy signal. For those locations that are not in the quiet time, the buffer may not be updated, but the accumulated signal can still subtracted. FIG. 57 illustrates an example of the notch filter of DSP 2904 accumulating in a buffer a replica of 3 cycles of noise in each of the quiet times 5702, 5704, 5706, 5708 and subtracting it from a noisy signal, according to some embodiments. As buffer contents 5710, 5712, 5714, 5716 match the noise data, respectively, in quiet times 5702, 5704, 5706, 5708, the noise can be modeled more accurately, and when subtracted, the noise content of the displayed signal can be reduced significantly.

As each sample is added to the buffer, the averaging can result in a filter that peaks at the line frequency 5802 and all harmonics (5804, 5806, and so on). This can selectively accumulate the line frequency and all harmonics and reject all other frequencies so that the notch filter of DSP 2904 only subtracts fixed frequency additive noise. FIG. 58 illustrates an example of the result of the notch filter, or buffer filter, of DSP 2904, according to some embodiments. To produce the buffer filter shown in FIG. 58, 5% of the new sample is added to 95% of the accumulated value to update the buffer, for example. In implementation specific situations, other combined percentages of each new sample and the accumulated value can be combined.

FIG. 59 is a flowchart for a method 5900 for notch filtering noise from an input signal, according to some embodiments. Method 5900 shall be described with reference to FIG. 29. However, method 5900 is not limited to that example embodiment.

In 5902, DSP 2904 accesses an input signal comprising noise having a first harmonic frequency and having noise. The frequency of the noise in the input signal can be substantially constant.

In 5904, DSP 2904 determines a quiet period in the input signal. DSP 2904 can determine the quiet period by calculating a slope of the input signal. DSP 2904 can then determine a presence of the quiet period based on the calculated slope being below a threshold value.

In 5906, during the quiet period, DSP 2904 stores samples of noise of the input signal in a buffer. The size of the buffer can be based on the frequency of the noise in the input signal.

As part of storing, DSP 2904 can average a sample of the input signal with a corresponding sample of noise in the buffer to create an average sample. DSP 2904 can then replace the corresponding sample of noise in the buffer with the average sample.

In 5908, DSP 2904 subtracts the samples from a single cycle of the noise in the buffer from the input signal to create a filtered signal. The subtracting can remove the first harmonic frequency and a second harmonic frequency from the input signal while avoiding introducing transient responses (e.g., ringing) in the filtered signal. The first harmonic frequency can be 60 Hz and the second harmonic frequency can be 120 Hz or 180 Hz.

In 5910, DSP 2904 repeats 5904 to 5908 to refine the filtered signal. As would be appreciated by a person of ordinary skill in the art, samples can be anywhere in the cycle. Moreover, the samples do not have to constitute a single cycle. In other words, DSP 2904 can store multiple cycles of noise of the input signal in the buffer.

In some embodiments, DSP 2904 can be based on a high-pass filter. Certain regions of the heart generate very low amplitude, high frequency signals that can be of interest during cardiac procedures. A physician often wants these signals to be highlighted for their review in the presence of noise and other larger cardiac signals.

This can be accomplished using a high-pass filter. FIG. 60 illustrates an example of a conventional high-pass filter 6002, according to some embodiments. In this case, the conventional high-pass filter's 3 db frequency 6004 can be approximately 200 Hz to suppress low frequencies. In addition, since the frequencies of interest are often above the line frequency (e.g., 60 Hz), the conventional high-pass filter approach can involve placing a notch 6006 there to eliminate interference from potential large powerline interference.

But a typical signal from the intracardiac catheters can contain high frequency signals from the conduction areas of the heart as well as sharp local spikes from various sources. FIG. 61 illustrates an example of a signal containing both high frequency signals from the conduction areas of the heart as well as sharp local spikes from various sources, according to some embodiments. As shown in FIG. 61, there is a sharp spike 6102 similar to a local near field impulse (e.g., QRS, local spike, transient, etc.) and a short burst of high frequency (e.g., 300 Hz) cardiac signal 6104.

FIG. 62 illustrates an example of the resulting output of filtering the signal of FIG. 61 using the high-pass filter of FIG. 60, according to some embodiments. As shown in FIG. 62, the low frequency content (e.g., baseline wander) is removed and the high frequency cardiac signal 6202 is highlighted as desired. However, the transient response of the high-pass filter can leave an impulse (e.g., artifact) 6204 and some ringing at the output which is not desired. In the midst of complex and larger waveforms, this impulse 6204 can be easily confused by a physician with the high frequency cardiac signal 6202. This is problematic for accurate diagnosis and treatment.

In some embodiments, DSP 2904 can be based on a high-pass filter that removes the impulse while allowing passage of the high frequency signal of interest. To remove the impulse, the input signal can be monitored for large excursions and high signal slope (e.g., derivative). When those conditions are present, the output can be blanked for a fixed period before and after that occurrence so that transient conditions do not show on the displayed waveforms. FIG. 63 illustrates an example of the resulting output of filtering the signal of FIG. 61 using a high-pass filter that removes an impulse 6302 while allowing passage of a high frequency cardiac signal 6304 of interest, according to some embodiments.

FIG. 64 is a flowchart for a method 6400 for high-pass filtering noise from an input signal, according to some embodiments. Method 6400 shall be described with reference to FIG. 29. However, method 6400 is not limited to that example embodiment.

In 6402, DSP 2904 accesses an input signal comprising noise and a high frequency signal of interest. In an application of DSP 2904, rapid conduction tissue recognition filtering can be performed to identify Purkinje fibers, high isotropy/low anisotropy segments from myocardial architecture, and preferential conducting pathways in disease tissue, for example. In such an application. DSP 2904 can access a Purkinje signal, for example, a high frequency signal of interest in the presence of noise. DSP 2904 can filter this input signal using a notch filter.

Artifacts, when recognized in the signal of interest, can be specifically introduced and characterized, and in turn, direct automation of filtering can be applied so as to use these diagnosed signals as a template to subtract/filter or otherwise process the signals out of the entirety of retrieved electrograms. For example, the system can record the signals with and without irrigation going through the catheter with constant catheter contact and catheter stability. The difference can represent the artifact, which can then be automatically characterized, a template created, and the template used to allow the system's filtering and summation techniques to remove the artifact. As would be understood by a person of ordinary skill in the art, such a system would be beneficial when employed in existing defibrillators as well as in subcutaneous implantable cardioverter defibrillators (ICDs).

In 6404, DSP 2904 high-pass filters the input signal to create a filtered signal.

In 6406, DSP 2904 isolates an artifact associated with the noise in the filtered signal from the high frequency signal of interest. For example, DSP 2904 can isolate an impulse response.

DSP 2904 can isolate the artifact by calculating a slope of the filtered input signal. DSP 2904 can then determine a presence of the artifact based on the calculated slope being above a threshold value. DSP can characterize the artifact in an artifact template. DSP 2904 can optionally select a filter based on the isolated artifact, such that the artifact template can be applied as the filter.

In 6408, DSP 2904 blanks the filtered signal for a fixed period of time before and after the isolated artifact. DSP 2904 can optionally perform the blanking using the selected filter. This blanking can remove the isolated artifact and allow passage of the high frequency signal of interest. DSP 2904 can buffer the filtered signal for the fixed period of time before and after the isolated artifact.

In some embodiments, DSP 2904 can perform pattern (or signal characteristic) matching. Pattern matching of cardiac signals can be based on some version of correlation. For example, the correlation can be a statistical correlation function or mean absolute deviation.

The correlation function (CF) can be specified by FORMULA 1.

$\begin{matrix} {{{Correlation}\mspace{14mu} {function}}\frac{\sum\limits_{i = 1}^{n}{\left( {X_{i} - \overset{\_}{X}} \right) \times \left( {Y_{i} - \overset{\_}{Y}} \right)}}{\sqrt{\sum\limits_{i = 1}^{n}{\left( {X_{i} - \overset{\_}{X}} \right)^{2} \times {\sum\limits_{i = 1}^{n}\left( {Y_{i} - \overset{\_}{Y}} \right)^{2}}}}}} & {{FORMULA}\mspace{14mu} 1} \end{matrix}$

Mean Absolute Deviation Function (MAD) cats be specified by FORMULA 2.

$\begin{matrix} {{{Correlation}\mspace{14mu} {function}}\frac{\sum\limits_{i = 1}^{n}{{\left( {X_{i} - \overset{\_}{X}} \right) - \left( {Y_{i} - \overset{\_}{Y}} \right)}}}{{\sum\limits_{i = 1}^{n}{\left( {X_{i} - \overset{\_}{X}} \right)}} + {\left( {Y_{i} - \overset{\_}{Y}} \right)}}} & {{FORMULA}\mspace{14mu} 2} \end{matrix}$

For surface ECGs, there can often be 12 leads in a set. In pace matching applications, all 12 leads may need to be correlated to all 12 leads of a reference beat. The reference beat can a beat taken from the patient when exhibiting an abnormal beat and compared to a paced beat from a catheter during an electrophysiology procedure. In other cases, only a subset of the leads may need to be correlated. In the case of the correlation function, a perfect match in shape can be +1 and direct opposite can be −1, and there can be no measure of amplitude similarity. For the MAD function, a perfect match can be 0, the direct opposite can be 1, and differences in amplitude can result in a poorer match.

For multiple lead comparisons, some measure of similarity may need to be established. This can be an average, a median value, or an extension of FORMULA 1 or FORMULA 2 to sum numerators and denominators for all leads in the set. In addition, more weight can be given to leads with larger amplitudes or to specific ranges of the beat that represent a feature to be emphasized (e.g., a Q wave).

In all comparisons, the leads can be normalized to have 0 DC offset. This may be because only the shape (and amplitude) are important in the comparisons.

In some embodiments, a pattern (or signal characteristic) can be selected using vertical calipers. Vertical calipers can be a GUI selection widget. FIG. 65 illustrates an example of a review window 6500 for selecting a range of data (usually one beat) using vertical calipers 6502, 6504, according to some embodiments.

The selected pattern can then be saved as a reference beat (or known signal pattern). FIG. 66 illustrates an example of saving a selected pattern as a reference beat, according to some embodiments. The Save New Pattern window 6600 shown in FIG. 66 can allow a user to view previously saved beats (e.g., known signal patterns) 6602 to decide if a newly identified beat is sufficiently unique relative to previously saved beats to merit saving separately. When a beat is stored it can be given a unique name 6604, color 6606, and/or description (i.e., comment) 6608.

When a user wants to initiate a search, the user can open a window of selectable patterns to search by clicking the Select Patterns button 6510 in the review window 6500 of FIG. 65. FIG. 67 illustrates an example of a Select Patterns to Search window 6700 of selectable patterns to search, according to some embodiments. The Select Patterns to Search window 6700 can display a scrollable list 6710 of all stored patterns. A check box 6720 on the left side of each list item can allow a user to select the associated pattern. The selections can remain active until the user decides to change them. When the user clicks on each pattern on the list 6710, the corresponding signal can be displayed in a window 6730 below the list box. The window 6730 can also display a field that allows the user to enter a confidence factor threshold value (also referred to as a pattern detection threshold 6740) that can be used to detect patterns. For example, pattern detection threshold 6740 is set to 80% in FIG. 67.

After the user has selected the patterns to search for and clicks OK 6750, the user can enable the search by clicking the Enable/Disable Patterns search button 6512 to start a search, which can become active in the review window 6500 shown in FIG. 65. After clicking on this button, a search for patterns can be started and beats that match the reference beat (e.g., confidence level is equal to or greater than the selected confidence factor threshold value) are displayed on the review window 6500. The found patterns can be displayed in two different modes of the review window 6500 of FIG. 65, a summary view and a detail view. A user can toggle between these two anodes using buttons Summary 6802, and Detail 6804, as shown in the review window 6800 of FIG. 68.

In summary view, the segments of the signals displayed in the review window that match the patterns can be highlighted with the colors associated with each pattern. Multiple patterns can overlap on the same segment of a signal. In summary view, the overlapping sections can be displayed in a different color to make the patterns more visible and discernable within each segment.

FIG. 68 illustrates an example of a pattern search summary view in the review window of FIG. 65, where multiple matching patterns are displayed, according to some embodiments. As shown in FIG. 68, four sections 6806, 6808, 6810, 6812 of surface ECG signals are highlighted in review window 6800. In this example, the two sections 6806, 6808 on the left side are displayed in two colors (or line styles), which can mean that these sections' patterns are overlapping. The two sections 6810, 6812 on the right side are displayed in the color assigned to pattern P1, which indicates that only the P1 pattern was found in those sections.

FIG. 69 illustrates an example of a pattern search summary view 6900 in the review window of FIG. 68 where a single matching pattern is displayed while other patterns are hidden, according to some embodiments. When matched patterns segments are displayed, a small window 6910 can be displayed on the right side. This window can allow a user to show or hide matched sections associated with each found pattern. In its initial state, all found patterns can be checked. When the user unchecks the checkbox 6912, 6914 beside each pattern name, the corresponding highlighted sections are hidden. As shown in FIG. 69, matched sections 6810, 6812 associated with pattern. PI 6916 are hidden. Therefore, the single-color sections 6810, 6812 in FIG. 68 that were on the right side and that were only matched with pattern P1 are not displayed in FIG. 69. However, the left sections 6806, 6808 in which pattern P1 and P4 were overlapping are now displayed in FIG. 69 in the color associated with pattern P4 6918.

In detail view, pattern details can be shown one segment at a time. Detail view can be enabled by selecting Detail 6804 in review window 6800 of FIG. 68. In detail view, the actual patterns can be displayed on top of matched segments using the color assigned to that pattern. FIG. 70 illustrates an example of a detail view for the signals in the review window of FIG. 65, according to some embodiments.

As shown in FIG. 70, detail view 7000 can show pattern details one segment at a time. For each section, if multiple patterns overlap, the pattern with the highest confidence factor can be initially shown. However, a user can select to see other overlapping patterns e.g., with lower confidence values) by checking their associated check box 7002, 7004 in the detailed view list 7006. In this case, the signals displayed in the detail view 7000 can be automatically changed to reflect the newly selected pattern. For example, as shown in FIG. 70, pattern P1 7008 has the highest confidence value (e.g., 87.0%) and therefore is initially shown.

In detail view, the confidence value per lead can be displayed using horizontal bars in a Confidence Factor Per Lead table 7010, and the actual confidence values can be provided on top of those bars as shown in FIG. 70. For example, lead I 7012 indicates a confidence value of 79.6%. Confidence values above the confidence level set by the user (e.g., when searched patterns were selected) can be displayed in green and values below this threshold can be displayed in orange, for example, visually indicating whether the confidence level for each individual lead meets the user's desired threshold. When the user clicks on any lead name in the Confidence Factor Per Lead table 7010, the corresponding pattern and the matched section on the signal can be displayed in a Pattern and Signal Traces window 7014 placed below the Confidence Factor Per Lead table 7010. Two buttons can be below this window to allow the user to change the time 7016 and amplitude scale 7018 on the displayed signals in order to accurately view the signals' shape details. If the selected time 7016 or amplitude scale 7018 make the signal partially visible, scroll bars can be automatically displayed to allow the user to access any part of the signals.

Detail view 7000 can also highlight the signal segment and the associated matched pattern that is displayed using brackets 7020. This can allow the user to easily identify the section of signal shown in the detail view 7000. The match confidence factor 7022 for that pattern can also be indicated beside one of the brackets.

FIG. 71 illustrates an example window 7100 having pattern match confidence values provided by lead (Confidence Factor Per Lead 7102), according to some embodiments. As shown in FIG. 71, leads V1 7104 and V2 7106 are below the confidence threshold and are shown in orange.

The concept of creating a template for specific artifact-producing events, as described for the method of FIG. 64, can also be used by the disclosed system in pattern matching. For example, a pattern of valve motion artifact related to unipolar signals collected above and below the valve, as well as within the coronary artery, can be used to create a pattern template for the operator to know immediately whether the catheter is above the valve, below the valve, or in the coronary artery. If the coronary artery profile within the pattern template is met, the system can respond by not allowing energy delivery during an ablation procedure, for example.

FIG. 72 is a flowchart for a method 7200 for pattern matching, according to some embodiments. Method 7200 shall be described with reference to FIG. 29. However, method 7200 is not limited to that example embodiment.

In 7202, DSP 2904 accesses an input cardiac signal.

In 7204, DSP 2904 matches a portion of the input cardiac signal to a known signal pattern. The known signal pattern can be captured during a previous patient procedure or a current patient procedure and stored in a pattern template. The known signal pattern can also be stored in a database.

DSP 2904 can match the portion of the input cardiac signal to the known signal pattern based on a correlation function. DSP 2904 can match the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function, for example. DSP 2904 can also match the portion of the input cardiac signal to the known signal pattern based on a confidence value.

In 7206, display module 2618 displays an indication of a degree of the match. The indication of the degree of the match can specify where to cardiac pace.

FIG. 73 is a flowchart for a method 7300 for pattern matching, according to some embodiments. Method 7300 shall be described with reference to FIG. 29. However, method 7300 is not limited to that example embodiment.

In 7302, DSP 2904 accesses an input cardiac signal.

In 7304, DSP 2904 accesses a detection threshold.

In 7306, DSP 2906 matches a portion of the input cardiac signal to a known signal pattern based on the detection threshold. The known signal pattern can be captured during a previous patient procedure or a current patient procedure. The known signal pattern can be stored in a database.

DSP 2904 can match the portion of the input cardiac signal to the known signal pattern based on a correlation function. DSP 2904 can match the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function, for example.

DSP 2904 can match the portion of the input cardiac signal to the known signal pattern based on weight specific areas of the known signal pattern. DSP 2904 can first match the portion of the input cardiac signal to the known signal pattern. DSP 2904 can determine a first confidence value based on the first matching. DSP 2904 can second match a portion of a second input signal to the known signal pattern. DSP 2904 can determine a second confidence value based on the second matching. DSP 2904 can average the first confidence value and the second confidence value to create an average confidence value. DSP 2904 can then determine the average confidence value is above the detection threshold.

In 7308, display module 2618 displays a highlighted portion of the input cardiac signal based on the matching. Display module 2618 can display the highlighted portion of the input cardiac signal based on a color associated with the known signal pattern, for example.

In some embodiments, DSP 2904 can perform late potential and early activation detection. By interpolating signal data from early sites of activation to the detected late sites of activation displayed independently with regular and late potential filters, the system can deduce a site of conduction delay. That site (or region) can be block highlighted with any compatible three-dimensional mapping system, which can allow a physician to guide catheter placement, document slow conduction at that site, and target that site for ablation. These features are very difficult, if not impossible, to accomplish with systems that saturate when applying gain to small signals, and thus slow conduction sites may otherwise be kept invisible to a physician.

Embodiments herein benefit by the high dynamic range of the system to interpolate data from early sites of activation to the detected late sites of activation, and to display the data independently with regular and late potential filters. Such embodiments are able to detect late potentials and early activations in the main signal display window both in real time (e.g., live) and during session playback. By clicking on a “create and manage searches” button in the main signal display window, a user can create search criteria for late potentials or early activations, activate a search, and manage existing searches.

FIG. 74 illustrates an example of a search definitions window 7400 for creating and managing searches for late potentials and early activations, according to some embodiments. To add a late potential search to a main signal display window, a user can click on an “Add Late Potentials Search” button 7402 within a search definitions window (e.g., the Search Definitions window 7400 of FIG. 74). In response, a late potential detection configuration window can be displayed, and various search parameters can be defined by the user. FIG. 75 illustrates an example of a late potentials detection configuration window 7500 for defining various search parameters for late potentials, according to some embodiments.

A user can create at least one pattern for performing a late potential search. The user can specify various late potential search parameters that allow for various types of searches. As shown in FIG. 75, a user can define one or more of the following parameters: name of the search (7502), selection of the beat pattern used for search (7504), reference point for the start of the search (7506), selection of which ECG lead will be used for beat detection (7508), selection of which intracardiac lead will be used for late potential detection (7510), a search interval using a starting point from the pattern reference and length (7512), a beat detection confidence threshold as a percentage (e.g., 80%) (7514), selection of a late potential detection confidence threshold as a percentage (e.g., 80%) (7516), and selection of a late potential amplitude threshold (e.g., 0.015 mV) (7518). As would be appreciated by a person of ordinary skill in the art, the user can define various other parameters.

Once all the parameters are defined, the search can be activated. When late potentials are detected, the signal display window can show the position of late potentials along their detection confidence. FIG. 76 illustrates an example signal display window 7600 showing the positions of late potentials 7602, 7604, 7606, 7608, 7610, along with their detection confidences, according to some embodiments. A review window can also display all the late potentials that are detected under a search results tab. The newly created late potential search can be listed within a search definitions window (e.g., the search definitions window 7400 of FIG. 74). The newly created late potential search can be listed within the search definitions window under a currently defined searches section.

A user can add an early activation search in a similar way as a late potential search. The user can specify various early activation search parameters that allow for various types of searches. The parameters can be equivalent to the late potential search parameters. The difference is that the search can occur in the search interval defined before the reference line. FIG. 77 illustrates an example of an early activation detection configuration window 7700 for defining various search parameters (similar to those described for FIG. 75) for early activations, according to some embodiments.

Once all the parameters are defined in the early activation detection configuration window 7700, the search can be activated. When early activations are detected, the signal display window can show the position of early activations along their detection confidence and length. FIG. 78 illustrates an example signal display window 7800 showing the positions of early activations 7802, 7804, 7806 along with their detection confidences, according to some embodiments. A review window can also display all the early activations that are detected under a search results tab. The newly created early activation search can be listed within a search definitions window (e.g., the search definitions window 7400 of FIG. 74). The newly created early activation search can be listed within the search definitions window under a currently defined searches section.

A user can manage already defined late potential and early activation searches using a search definitions window. FIG. 79 illustrates an example of a search definitions window 7900 for managing already defined late potential and early activation searches, according to some embodiments.

In the search definitions window 7900, all of the active searches can be listed in the Currently Defined Searches window 7902, and a user can run, stop, delete, or modify the searches. If a search is stopped, the user can resume running the search by clicking on a “run” button 7904. For example, as shown in FIG. 79, search EA1 is stopped 7906 and search LP1 is running 7908. In this case, the user can resume running the EA1 search and stop 7910 running the LP1 search or use other options (e.g., delete 7912 and modify 7914).

FIG. 80 is a flowchart for a method 8000 for detecting early activations or late potentials, according to some embodiments. Method 8000 shall be described with reference to FIG. 29. However, method 8000 is not limited to that example embodiment.

In 8002, a first DSP 2904 accesses a first cardiac signal associated with a surface lead.

In 8004, the first DSP 2904 matches a beat of the first cardiac signal to a known signal pattern. The first DSP 2904 can match the beat of the first cardiac signal to the known signal pattern based on a correlation function. The first DSP 2904 can match the beat of the first cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function, for example. The first DSP 2904 can match the beat of the first cardiac signal to the known signal pattern based on a confidence value. The confidence value can be user-defined.

In 8006, a second DSP 2904 searches for a period of time before and after the matched beat for an early activation or a late potential in a second cardiac signal. The period of time can be a user-defined period.

The second DSP 2904 can search a buffer comprising a portion of the second cardiac signal for the early activation or the late potential. The second DSP 2904 can search for the early activation based on an amplitude threshold value.

Using the early activation or the late potential, the system can interpolate signal data from a catheter at a site of the early activation to a site of the late potential. The system can display that signal data independently with regular and late potential filters. Using the interpolated signal data, the system can deduce a site of conduction delay. The system can also, in combination with a three-dimensional mapping system, use the interpolated signal data at a site to guide further catheter placement, document slow conduction at that site, or target that site for ablation.

In some embodiments, display module 2618 can display one or more signals using a waterfall view (e.g., the waterfall views in FIGS. 37A and 37B). A waterfall view window can stack vertically heart beats that match a selected pattern on a specific ECG lead and can show beside each detected beat a user selected intracardiac signal. The latter can be shown for a user defined interval relative to a reference point within the beat pattern.

To set up parameters for a waterfall view, a user can click on a “create waterfall view window” button located in the main signal display toolbar. In response, a waterfall display configuration window can be displayed. FIG. 81 illustrates an example of a waterfall display configuration window 8100, according to some embodiments.

As shown in FIG. 81, a user can define one or more of the following parameters. The user can select a beat pattern 8102 to search (e.g., can be selected from already saved beat patterns that will be used in waterfall view). The user can define a reference point 8104 on the beat pattern that will be used for the display interval. If a reference point is not already selected, the user can add the reference point by clicking on a beat pattern display window located under the list of beat patterns. Similarly, the location of an existing reference point can be changed by clicking on the beat pattern display window. The user can select a surface ECG lead 8106 for beat detection. The user can define a display interval 8108 for the ECG lead (e.g., a start point relative to pattern reference point and length). The user can select an intracardiac channel 8110 for search. The user can define a display interval 8112 for the intracardiac lead (e.g., start point relative to pattern reference point and length). The user can also select a vertical scrolling mode 8114 such as time or beat.

FIG. 82 illustrates an example of a waterfall view 8200 using time mode, according to some embodiments. When vertical scrolling mode 8114 is set to time mode, the matched signals can scroll up continuously with time. Therefore, when no beats matching the selected pattern are detected, time mode can show gaps 8202 between beats. In time mode, the last beat time stamp 8204 can be shown on the lower left corner of the window.

When vertical scrolling mode 8114 is set to beat mode, the vertical auto scroll of the waterfall view window can be disabled and beats can be scrolled up only as new beats matching the selected pattern are detected. FIG. 83 illustrates an example of a waterfall view 8300 using beat mode, according to some embodiments. In beat mode, each individual beat can be time stamped 8302.

Once all of the parameters for a waterfall view are defined by a user, a waterfall view window can display the two signals side by side, as shown in both FIG. 82 and FIG. 83. The waterfall view window can display the signals using either time mode or beat mode. The name of the leads 8304, 8306 can be shown on top of the window. The beat pattern name 8208 can also be shown beside the ECG lead name 8206.

There can be buttons within the waterfall view window's toolbar, for example, a waterfall parameters button 8210 and display parameters button 8212. The waterfall parameters button 8210 can allow a user to adjust display parameters while the waterfall view window is open. For example, the user can change the display interval, vertical scrolling mode, or any parameters as would be appreciated by a person of ordinary skill in the art.

The user can disable this feature. FIG. 84 illustrates an example of a display parameters window 8400, according to some embodiments. The display parameters window 8400 can allow a user to change various display parameters. For example, the user can adjust a zoom 8402, 8404 for each lead with an option to reset 8416, 8418 to default. The user can add 8406 or remove 8408 clipping. The user can change a color 8410, 8412 for each lead or subset of leads. The user can disable fading 8414 of displayed beats. In some embodiments, displayed beats can fade as they move toward the upper part of the waterfall view window.

In some embodiments, an EP hardware system can produce a clean unipolar signal, according to some embodiments. The EP hardware system can produce a clean unipolar signal based on it having an ECG circuit board and a plurality of IC circuit boards that share substantially the same circuit configuration and components, and the ECG circuit board processing the ECG signal using substantially the same path as each IC circuit board uses to process its corresponding IC signal. A single Wilson Central Terminal (WCT) signal can be used for the ECG circuit board and the plurality of IC circuit boards.

In some embodiments, an EP hardware system can act as a central processing system for all other systems. The EP hardware system can include an ECG circuit board configured to receive an ECG signal, a plurality of IC circuit boards each configured to receive an IC signal, a communications interface communicatively coupled to a remote device, and a processor, coupled to the ECG circuit board, the plurality of IC circuit boards, and the communications interface. The EP hardware system can act as a central processing system by having its processor receive, via the communications interface, feedback from the remote device, and control, via the communication interface, the remote device based on the ECG signal, the IC signals, and the feedback from the remote device.

The EP hardware system can receive feedback from, and control, a remote device selected from the group consisting of, but not limited to, an ultrasound machine, a radio frequency (RF) generator, a stimulator, a three-dimensional imaging device, an intra-cardiac echocardiography (ICE) machine, a fluoroscopy machine, and a defibrillator. As would be appreciated by a person of ordinary skill in the art, the remote device can be various other types of device. The EP hardware system can communicate with the remote device over the communications interface coupled to the remote device using a communication protocol selected from the group consisting of, but not limited to, Digital Imaging and. Communications in Medicine (DICOM), Ethernet, Universal Serial Bus (USB), and Institute of Electrical and Electronics Engineers (IEEE) 802.11. As would be appreciated by a person of ordinary skill in the art, the EP hardware system can communicate with the remote device using various other communication protocols.

Computer System Implementation

Various embodiments can be implemented, for example, using one or more well-known computer systems, such as computer system 8500 shown in FIG. 85, One or more computer systems 8500 can be used, for example, to implement any of the embodiments discussed herein, as well as combinations and sub-combinations thereof.

Computer system 8500 can include one or more processors (also called central processing units, or CPUs), such as a processor 8504. Processor 8504 can be connected to a communication infrastructure or bus 8506.

Computer system 8500 can also include user input/output device(s) 8503, such as monitors, keyboards, pointing devices, etc., which can communicate with communication infrastructure 8506 through user input/output interface(s) 8502.

One or more of processors 8504 can be a graphics processing unit (GPU). In an embodiment, a GPU can be a processor that is a specialized electronic circuit designed to process mathematically intensive applications. The GPU can have a parallel structure that is efficient for parallel processing of large blocks of data, such as mathematically intensive data common to computer graphics applications, images, videos, etc.

Computer system 8500 can also include a main or primary memory 8508, such as random access memory (RAM). Main memory 8508 can include one or more levels of cache. Main memory 8508 can have stored therein control logic (e.g., computer software) and/or data.

Computer system 8500 can also include one or more secondary storage devices or memory 8510. Secondary memory 8510 can include, for example, a hard disk drive 8512 or a removable storage device or drive 8514. Removable storage drive 8514 can be a floppy disk drive, a magnetic tape drive, a compact disk drive, an optical storage device, tape backup device, or any other storage device/drive.

Removable storage drive 8514 can interact with a removable storage unit 8518. Removable storage unit 8518 can include a computer usable or readable storage device having stored thereon computer software (control logic) or data. Removable storage unit 8518 can be a floppy disk, magnetic tape, compact disk, DVD, optical storage disk, or any other computer data storage device. Removable storage drive 8514 can read from or write to removable storage unit 8518.

Secondary memory 8510 can include other means, devices, components, instrumentalities, or other approaches for allowing computer programs or other instructions or data to be accessed by computer system 8500. Such means, devices, components, instrumentalities, or other approaches can include, for example, a removable storage unit 8522 and an interface 8520. Examples of the removable storage unit 8522 and the interface 8520 can include a program cartridge and cartridge interface (such as that found in video game devices), a removable memory chip (such as an EPROM or PROM) and associated socket, a memory stick and USB port, a memory card and associated memory card slot, or any other removable storage unit and associated interface.

Computer system 8500 can further include a communication or network interface 8524. Communication interface 8524 can enable computer system 8500 to communicate and interact with any combination of external devices, external networks, external entities, etc. (individually and collectively referenced by reference number 8528). For example, communication interface 8524 can allow computer system 8500 to communicate with external or remote devices 8528 over communications path 8526, which can be wired or wireless (or a combination thereof, and which can include any combination of LANs, WANs, the Internet, etc. Control logic or data can be transmitted to and from computer system 8500 via communications path 8526.

Computer system 8500 can also be any of a personal digital assistant (PDA), desktop workstation, laptop or notebook computer, netbook, tablet, smart phone, smart watch or other wearable, appliance, part of the Internet-of-Things, or embedded system, to name a few non-limiting examples, or any combination thereof.

Computer system 8500 can be a client or server, accessing or hosting any applications or data through any delivery paradigm, including but not limited to remote or distributed cloud computing solutions; local or on-premises software (“on-premise” cloud-based solutions); “as a service” models (e.g., content as a service (CaaS), digital content as a service (DCaaS), software as a service (SaaS), managed software as a service (MSaaS), platform as a service (PaaS), desktop as a service (DaaS), framework as a service (FaaS), backend as a service (BaaS), mobile backend as a service (MBaaS), infrastructure as a service (IaaS), etc.); or a hybrid model including any combination of the foregoing examples or other services or delivery paradigms.

Any applicable data structures, file formats, and schemas in computer system 8500 can be derived from standards including but not limited to JavaScript Object Notation (JSON), Extensible Markup Language (XML), Yet Another Markup Language (YAML), Extensible Hypertext Markup Language (XHTML), Wireless Markup Language (WML), MessagePack, XML User Interface Language (XUL), or any other functionally similar representations alone or in combination. Alternatively, proprietary data structures, formats or schemas can be used, either exclusively or in combination with known or open standards.

In some embodiments, a tangible, non-transitory apparatus or article of manufacture including a tangible, non-transitory computer useable or readable medium having control logic (software) stored thereon can also be referred to herein as a computer program product or program storage device. This includes, but is not limited to, computer system 8500, main memory 8508, secondary memory 8510, and removable storage units 8518 and 8522, as well as tangible articles of manufacture embodying any combination of the foregoing. Such control logic, when executed by one or more data processing devices (such as computer system 8500), can cause such data processing devices to operate as described herein.

Based on the teachings contained in this disclosure, it will be apparent to persons skilled in the relevant art how to make and use embodiments of this disclosure using data processing devices, computer systems, or computer architectures other than that shown in FIG. 85. In particular, embodiments can operate with software, hardware, and/or operating system implementations other than those described herein.

Conclusion

The EP recording system disclosed herein effectively removes noise and removes or isolates unwanted large signals while preserving relevant components of raw small signals, that is, while preserving integrity of original information in an EP environment. Conventional EP systems can successfully filter out noise but may also filter out signal components with the noise that a medical team desires to see. Conventional EP systems can also generate and introduce additional noise and unwanted artifacts not originally present in the raw signals with well-meaning software filtering algorithms. Even when conventional EP systems utilize state-of-the-art noise reduction practices, conventional EP systems cannot effectively collect clean small signals with high confidence in the presence of simultaneous large-signal procedures such as defibrillation and ablation. This is because conventional EP systems do not have a comprehensive signal acquisition and filtering solution across the relevant frequency ranges—low (e.g., 0 to 100 Hz), mid (e.g., above 100 Hz to below 300 kHz), and high (e.g., above and including 300 kHz)—and cannot effectively handle simultaneous signals that differ by 100 s or 1000 s of orders of magnitude. In comparison, the EP recording system disclosed herein integrates and applies novel hardware circuitry, software methods, and system topologies to remove unwanted signals but preserve original signal waveforms across the relevant frequencies for signals found in an EP environment.

The disclosed EP system does not have to make tradeoffs that conventional EP systems have to make. Rather, the disclosed EP system allows aspects of hardware and software to perform in tandem, in order to simultaneously: (1) run amplifiers at high gain to see small signals, (2) prevent both clipping and saturation by minimizing destructive large-signal filtering in hardware to see the large signals at the same time, (3) process the signals, separating them from each other in independent displays, removing any remaining noise, and synchronizing separated signals, and finally (4) enable a user to manipulate and analyze both large and small signals so that signal artifacts and events can be accurately time-and-event correlated.

The exemplary signals 2200 of FIGS. 22A-22B illustrate these concepts, showing the improvement in the visualization of an ECG or IC cardiac signal in the presence of large transients, ablation signals, defibrillation signals, and EP environment noise after being acquired, filtered, and processed by the EP system disclosed herein. FIG. 22A shows the removal of noise from both small and large signals, and the avoidance of clipping in the processing of large signals. A conventional EP system may provide a noisy cardiac signal 2203 and artificially clip a signal 2202 to limit the amplitude of a displayed signal to avoid the effects of saturation. The disclosed EP system acquires and clearly displays both weak 2214 and strong 2205 signals. With the disclosed EP system, there is no need for artificial clipping, and a strong signal 2204 is fully defined (not clipped).

FIG. 22B illustrates the EP system's ability to reveal low-amplitude cardiac signals and micro-components of relevant random artifacts of an EP signal in the presence of noise and large-signal procedures. The window 2216 illustrates a noisy signal 2208 with both the high and low-amplitude micro-components 2206 of the desired signal revealed by the disclosed EP system. In comparison, as shown in window 2218, a conventional EP system may not as successfully reveal both low and high-amplitude micro-components of the desired signal. With noisier signals, a low-amplitude micro-component 2210 of the desired signal can be revealed but is more apt to be lost amongst the noise 2212 in a conventional EP system. A high-amplitude micro-component 2211 of the desired signal may be lost by artificial clipping in a conventional EP system.

FIG. 22C illustrates the ability of the disclosed EP system to remove 60 Hz noise 2220, without saturation or delayed recovery, while preserving the component 2222 of the 60 Hz signal that belongs to the original waveform 2224. Specifically, component 2222, of the original waveform 2224, which occurs at the same time as the artifact 2220, is not lost. In other words, when large signals simultaneously overlap small signals, the disclosed EP system can identify, acquire, and process both cleanly.

It is to be appreciated that the Detailed Description section, and not any other section, is intended to be used to interpret the claims. Other sections can set forth one or more but not all exemplary embodiments as contemplated by the inventor(s), and thus, are not intended to limit this disclosure or the appended claims in any way.

While this disclosure describes exemplary embodiments for exemplary fields and applications, it should be understood that the disclosure is not limited thereto. Other embodiments and modifications thereto are possible, and are within the scope and spirit of this disclosure. For example, and without limiting the generality of this paragraph, embodiments are not limited to the software, hardware, firmware, or entities illustrated in the figures or described herein. Further, embodiments (whether or not explicitly described herein) have significant utility to fields and applications beyond the examples described herein.

Embodiments have been described herein with the aid of functional building blocks illustrating the implementation of specified functions and relationships thereof. The boundaries of these functional building blocks have been arbitrarily defined herein for the convenience of the description. Alternate boundaries can be defined as long as the specified functions and relationships (or equivalents thereof) are appropriately performed. Also, alternative embodiments can perform functional blocks, steps, operations, methods, etc. using orderings different than those described herein. This disclosure also extends to methods associated with using or otherwise implementing the features of the disclosed hardware and systems herein.

References herein to “one embodiment,” “an embodiment,” “an exemplary embodiment,” or similar phrases, indicate that the embodiment described can include a particular feature, structure, or characteristic, but every embodiment cannot necessarily include the particular feature, structure, or characteristic. Moreover, such phrases are not necessarily referring to the same embodiment. Further, when a particular feature, structure, or characteristic is described in connection with an embodiment, it would be within the knowledge of persons skilled in the relevant art to incorporate such feature, structure, or characteristic into other embodiments whether or not explicitly mentioned or described herein. Additionally, some embodiments can be described using the expression “coupled” and “connected,” along with their derivatives. These terms are not necessarily intended as synonyms for each other. For example, some embodiments can be described using the terms “connected” or “coupled” to indicate that two or more elements are in direct physical or electrical contact with each other. The term “coupled,” however, can also mean that two or more elements are not in direct contact with each other, but yet still co-operate or interact with each other.

The breadth and scope of this disclosure should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents. 

What is claimed is:
 1. A computer implemented method, comprising: accessing, by at least one processor, an input cardiac signal; matching, by the at least one processor, a portion of the input cardiac signal to a known signal pattern; and displaying, by the at least one processor, an indication of a degree of the match.
 2. The method of claim 1, wherein the known signal pattern is captured during a previous patient procedure or a current patient procedure and is stored in a pattern template.
 3. The method of claim 1, wherein the known signal pattern is stored in a database.
 4. The method of claim 1, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on a correlation function.
 5. The method of claim 1, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function.
 6. The method of claim 1, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on a confidence value.
 7. The method of claim 1, wherein the indication of the degree of the match specifies where to cardiac pace.
 8. A non-transitory computer-readable device having instructions stored thereon that, when executed by at least one computing device, cause the at least one computing device to perform operations comprising: accessing an input cardiac signal; matching a portion of the input cardiac signal to a known signal pattern; and displaying an indication of a degree of the match.
 9. The non-transitory computer-readable device of claim 8, wherein the known signal pattern is captured during a previous patient procedure or a current patient procedure and is stored in a pattern template.
 10. The non-transitory computer-readable device of claim 8, wherein the known signal pattern is stored in a database.
 11. The non-transitory computer-readable device of claim 8, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on a correlation function.
 12. The non-transitory computer-readable device of claim 8, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function.
 13. The non-transitory computer-readable device of claim 8, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on a confidence value.
 14. The non-transitory computer-readable device of claim 8, wherein the indication of the degree of the match specifies Where to cardiac pace.
 15. A computer implemented method, comprising: accessing, by at least one processor, an input cardiac signal; accessing, by the at least one processor, a detection threshold; matching, by the at least one processor, a portion of the input cardiac signal to a known signal pattern based on the detection threshold; and displaying, by the at least one processor, a highlighted portion of the input cardiac signal based on the matching.
 16. The method of claim 15, wherein the known signal pattern is captured during a previous patient procedure or a current patient procedure.
 17. The method of claim 15, wherein the known signal pattern is stored in a database.
 18. The method of claim 15, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on a correlation function.
 19. The method of claim 15, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function.
 20. The method of claim 15, wherein the matching further comprises: first matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern; determining, by the at least one processor, a first confidence value based on the first matching; second matching, by the at least one processor, a portion of a second input signal to the known signal pattern; determining, by the at least one processor, a second confidence value based on the second matching; averaging, by the at least one processor, the first confidence value and the second confidence value to create an average confidence value; and determining, by the at least one processor, the average confidence value is above the detection threshold.
 21. The method of claim 15, wherein the displaying further comprises: displaying, by the at least one processor, the highlighted portion of the input cardiac signal based on a color associated with the known signal pattern.
 22. The method of claim 15, wherein the matching further comprises: matching, by the at least one processor, the portion of the input cardiac signal to the known signal pattern based on weight specific areas of the known signal pattern.
 23. A non-transitory computer-readable device having instructions stored thereon that, when executed by at least one computing device, cause the at least one computing device to perform operations comprising: accessing an input cardiac signal; accessing a detection threshold; matching a portion of the input cardiac signal to a known signal pattern based on the detection threshold; and displaying a highlighted portion of the input cardiac signal based on the matching.
 24. The non-transitory computer-readable device of claim 23, wherein the known signal pattern is captured during a previous patient procedure or a current patient procedure.
 25. The non-transitory computer-readable device of claim 23, wherein the known signal pattern is stored in a database.
 26. The non-transitory computer-readable device of claim 23, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on a correlation function.
 27. The non-transitory computer-readable device of claim 23, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on a mean absolute deviation (MAD) function.
 28. The non-transitory computer-readable device of claim 23, wherein the matching further comprises: first matching the portion of the input cardiac signal to the known signal pattern: determining a first confidence value based on the first matching; second matching a portion of a second input signal to the known signal pattern; determining a second confidence value based on the second matching; averaging the first confidence value and the second confidence value to create an average confidence value; and determining the average confidence value is above the detection threshold.
 29. The non-transitory computer-readable device of claim 23, wherein the displaying further comprises: displaying the highlighted portion of the input cardiac signal based on a color associated with the known signal pattern.
 30. The non-transitory computer-readable device of claim 23, wherein the matching further comprises: matching the portion of the input cardiac signal to the known signal pattern based on weight specific areas of the known signal pattern. 